Stretch Valve Balloon Catheter and Methods for Producing and Using Same

ABSTRACT

A safety catheter for draining a given fluid includes a hollow stretch valve and a flexible, multi-lumen, balloon drainage catheter having a proximal catheter end, a balloon defining a balloon interior to be inflated with an inflation fluid, a drain lumen. and a balloon drainage port fluidically connecting the balloon interior to the drain lumen. The hollow stretch valve is shaped to permit the given fluid to pass therethrough and is positioned in the drain lumen to at least partially slide therein such that, in a steady state, the stretch valve prevents the inflation fluid from passing through the drainage port, and, in a stretched state when the proximal catheter end is stretched, the distal sliding portion slides within the drain lumen to permit the inflation fluid to pass through the drainage port and into the drain lumen.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application:

-   -   is a continuation of U.S. patent application Ser. No.        14/024,151, filed Sep. 11, 2013; and    -   is a divisional of U.S. patent application Ser. No. 13/707,752,        filed Dec. 7, 2012 (which application claims the benefit under        35 U.S.C. §119(e) of U.S. provisional application No.        61/637,690, filed Apr. 24, 2012); and    -   is a continuation-in-part of U.S. patent application Ser. No.        13/713,205, filed Dec. 13, 2012;    -   is a continuation-in-part of U.S. patent application Ser. No.        12/943,453, filed Nov. 10, 2010, now U.S. Pat. No. 8,382,708        (which application claims the benefit under 35 U.S.C. §119(e) of        U.S. provisional application No. 61/260,271 filed Nov. 11,        2009); and    -   is a continuation-in-part of U.S. patent application Ser. No.        11/339,258, filed Jan. 25, 2006, now U.S. Pat. No. 7,883,503        (which application claims the benefit under 35 U.S.C. §119(e) of        U.S. Provisional Patent Application Nos. 60/647,204 and        60/647,205, both filed Jan. 26, 2005),        the prior applications are hereby incorporated herein by        reference in their entirety.

BACKGROUND OF THE INVENTION

1. Field of the Invention

The present invention relates to a catheter, especially an automaticallydeflating balloon catheter with a stretch valve and methods for usingand manufacturing such a catheter.

2. Description of Related Prior Art

A number of conventional balloon catheters exist in the prior art. Somecatheters are used to drain the bladder of a patient during surgicalprocedure or to treat bladder and/or urethra or prostate conditions, forexample. For example, a common balloon catheter made by RUSCH® andreferred to as a Foley catheter is widely used today for treating anddraining a patient's bladder. The Foley catheter is shown in FIG. 1 andhas a multi-lumen shaft 1 that is disposed in the urethra 10, a balloonportion 3 disposed at the distal end of the shaft 1, a fluid drainsection 4 disposed at the distal end of the balloon 3, and a curved orstraight, distal guiding tip 5 at the distal-most end of the entirecatheter. When placed properly, the proximal-most side of the inflatedballoon 3 rests on the interior wall 31 of the bladder 30, entirelyblocking off the urethrovesical junction 11 connecting the bladder 30and the urethra 10. In such a position, the fluid drain section 4 allowscontinuous drainage of the bladder 30 and the balloon 3 virtuallyentirely prevents the catheter from slipping out of the bladder. Thisideally inserted position is shown in FIG. 1. As used herein, a fluidcan be either a liquid or a gas. Exemplary fluids for inflating aballoon 3 are saline, sterile water, air, or carbon dioxide gas.Exemplary fluids drained by the catheters mentioned herein include urineand blood.

Basically, the catheter has a tube-like body with two lumens passingtherethrough. The larger lumen is open to the bladder (distally) andempties into a non-illustrated ex-corporeal bag (proximally) foreventual disposal. A smaller lumen is used to inflate (and deflate) theballoon 3 with sterile water (typically) using a syringe attached to theinflation lumen fitting 260 (see, e.g., FIG. 3). When inflated in thebladder, for example, the catheter is substantially prevented fromsliding out of the urethra in use.

In a conventional balloon 3, the balloon 3 has a substantially constantballoon wall thickness. The balloon 3 is fixed to the outer surface of afluid drainage line (not illustrated in FIG. 1) and is not intended tobe removed therefrom or to burst thereon unless an extraordinary amountof inflation occurs. If such an event happens, the material of theballoon will open at a random location based upon the microscopicfractures or weaknesses in the material itself. Such a tearing event isnot supposed to occur under any circumstances during use with a patient.

Prior art catheters are not constructed to prevent tearing of theurethra during a catheter implanting procedure and are not constructedto break in any predefined way. Prior art catheters are designed todeflate only when actively deflated, either by a syringe similar to theone that inflated it or by surgery after the physician diagnoses theballoon as not being able to deflate, in which circumstance, a procedureto pop the balloon surgically is required.

Over 96 million indwelling catheters are sold worldwide on an annualbasis. Twenty four million catheters are sold to hospitals in the U.S.There are numerous complications associated with those catheters thatneed to be prevented. These complications are responsible for increasesin hospital stays, excessive bleeding, mortality, as well as morbidity.They also cause an increased expense and burden on the already-stressedhealth care system.

The complications result from several different mechanisms. First, andprobably most common, is improper placement of the catheter. Because ofthe unique anatomy of the male urethra, placing a urethral catheter forurinary drainage can be difficult. A problem arises when the physician,technician, or nurse thinks that the catheter is actually in a properposition when it is not. The proper position for the catheter is withthe balloon located in the cavity of the bladder. In this position, thetip distal to the balloon is located in the bladder and is used to drainthe bladder cavity.

For placement of this catheter in the bladder 30 in the ideal position,however, the physician or technician has no visual aid. As shown in FIG.1, the wall 40 defining the urethrovesical junction 11 is very short inthe longitudinal direction of the urethra 10. If the physician insertsthe catheter too far into the bladder 30, no damage occurs from ballooninflation; however, there is a possibility of leakage around the balloon3, which, under normal conditions, actually helps to lubricate theurethra 10. In such a case, gentle proximal movement of the shaft 1 willplace the proximal side of the balloon 3 against the urethrovesicaljunction 11. The bladder 30 can then easily expand and stretch tocompensate for the balloon 3. A normal bladder capacity is 400 cc to 500cc. A normal balloon capacity is approximately 10 cc to 12 cc althoughlarger balloons are sometimes used. A typical balloon is 5 cc, however,most clinicians put 10 cc of water in the balloon for inflation. With 5cc of water in the balloon, the diameter is approximately 2 cm and with10 cc the diameter is approximately 2.5 cm.

Complications occur when the technician and/or nurse inflates theballoon when the balloon is not in the bladder. If the technician doesnot insert the catheter in far enough, then the balloon 3 will beinflated within the urethra 10—a condition that, while common, is to beavoided at all costs and is a frequent cause of bladder infectionscreated during a hospital or clinic visit. Infections arise becauseinflation of the bladder 3 inside the urethra 10 causes the urethra 10to stretch too far and tear. Even though the urethra 10 is a flexibletube, it has limits to which it can be safely stretched from within.Almost every balloon catheter has a balloon outer diameter/circumferencethat well-exceeds the safe stretching limit of the urethra 10.Therefore, if the balloon catheter is not inserted far enough, inflationof the balloon 3 will cause serious injury to the urethra 10. This isespecially true with elderly patients who have urethras that are not aselastic as younger patients. Also, just as important is the change inanatomy of older males, in particular, the prostatic portion of theurethra. With age, the prostate becomes larger and, sometimes, thecatheter cannot be advanced through the prostatic portion of theurethra. When this occurs, the technician does not insert the catheterall the way into the bladder and inflates the balloon within theurethra. Alternatively, strictures, i.e., scar tissue, cause thecatheter to halt and further pressure tears the urethral wall to createa new, unintended passage. Both of these improper insertions causesevere bleeding and damage.

The elastomeric balloon of present-day catheter products requiresrelatively high pressures to initiate inflation and expand to anexpected full-diameter shape upon over-inflation. As such, whenincorrectly placed in the urethra, the rapid inflation, combined withthe high-pressure, causes the balloon to tear the surrounding membrane,referred to as the mucosa. Tearing of the urethra 10 in this way causesbleeding and allows bacteria to enter into the bloodstream at the tearsite, thus causing the subsequent bladder infection. Significantbleeding can become life threatening. The urethra can normally dilateseveral millimeters; however, when the balloon is inflated, thisdilation is usually several centimeters. Also, without sufficient andimmediate venting of the balloon inflation fluid after improperplacement, an accidental or intentional pull on the catheter externallycan and does cause extensive bodily harm to the patient.

Life threatening bleeds, especially in patients who are anticoagulated,can and do occur. Also when the urine is infected, as inimmunocompromised patients and the elderly, the bacteria enter the bloodstream and can cause serious infections (e.g., sepsis), which frequentlycan lead to death. If the patient survives the initial trauma, thenlong-term complications, such as strictures, can and usually do occur.Strictures cause narrowings within the urine channel and usually requireadditional procedures and surgeries to correct.

Other mechanisms of catheter-induced injuries are inadvertentmanipulation of the tubing or dislodging of the balloon—caused when thecatheter is pulled from outside the patient due to a sudden jerk ortension. This commonly happens when the patient is ambulating ortraveling from the bed to the commode or bathroom. The tubing mayinadvertently become fixed while the patient is still moving, at whichtime a sudden jerk is imparted upon the balloon and pulls the ballooninto the urethra, which tears the urethra, causing severe pain andbleeding. Injury caused by the improper, inadvertent, and/or earlyremoval of an inflated balloon catheter is referred to as iatrogenicinjury (also referred to as an in-hospital injury). Hundreds ofthousands of such iatrogenic injuries occur each year—all of which needto be prevented, not only for patient safety, but also because the costimposed on the medical health industry for each injury is enormous.

Yet another scenario occurs when the patient deliberately pulls on thecatheter, thereby causing self-induced pain and injury to the urethra.This commonly happens in confused patients, for example, patients innursing homes who have a disease or cognitive dysfunction problem, suchas Alzheimer's disease, or other diseases that make the patient unableto understand the necessity of having a catheter. Confusion occurs whenthe patient has a spasm causing pain and a strong urge to urinate.During the spasm, the confused patient often tugs and pulls on acatheter, which results in injury. Like iatrogenic injuries, theseself-induced injuries must be prevented. In the particular case ofinjury caused by catheter withdrawal when the balloon is inflated(either iatrogenic or self-induced), hospitals have categorized suchinjuries as “never events”—occurrences that should never happen. Undersuch circumstances, insurance typically does not cover the resultingextensive medical expenses.

The injuries mentioned herein are not limited to males and also causesevere damage to the female bladder and urethra. The injuries can alsooccur post-surgically, which makes the damage even more severe. Onecommon situation where injury is caused is when the patient is medicatedwith morphine or other analgesics that render the patient confused andunable to make rational decisions. Feeling the foreign body inside theurethra, the confused patient does not know to leave it alone and,instead, gives it the injury-causing tug. These injuries have beenwell-documented and are not limited to adults. Numerous injuries aredocumented in pediatric patients.

Usually, it takes time to make a diagnosis of patient-caused catheterinjury. Immediately after diagnosing the injury, a technician needs todeflate the catheter. However, once the urethra is torn, replacing thedamaged catheter with another catheter is quite difficult and, in fact,exacerbates the injury. Sometimes, the patient has to be taken to theoperating room to replace a urinary drainage tube once the injuryoccurs. Because catheters and leg bags are now used routinely in certainsituations during home health care, this scenario is not limited tohospitals and occurs at nursing homes and patients' homes as well.

Most of the recent catheter technology has been focused on reducingurinary tract infections that are caused by catheters, injuries that areusually the most common catheter-related complications. One example ofsuch technology is impregnation of the catheter with antimicrobials orantibiotics. But, these advances do nothing to prevent the injuriesexplained herein.

Accordingly, it would be beneficial to provide a balloon catheter thatdoes not inflate past the tearing limit of a urethra and deflates in adesired, predefined way under certain conditions.

SUMMARY OF THE INVENTION

It is accordingly a desire to provide an automatically deflatingpressure balloon catheter with a stretch valve and methods formanufacturing and using the catheter that overcome thehereinafore-mentioned disadvantages of the heretofore-known devices andmethods of this general type and quickly and rapidly deflates if pulledout prior to physician-scheduled deflation of the balloon.

With the foregoing and other objects in view, there is provided, inaccordance with the invention, a safety catheter including a hollowstretch valve and a flexible, multi-lumen shaft having an outerdiameter, a distal tip, and a proximal catheter end with a drain end.The multi-lumen shaft defines a drain lumen extending through the shaftand shaped to drain fluid adjacent the distal tip therethrough and outthe drain end, a distal hollow balloon portion defining a ballooninterior and having at least one inflation port fluidically connected tothe balloon interior, the balloon portion inflating outwardly to adiameter greater than the outer diameter of the shaft when inflated withinflation fluid, at least one inflation lumen parallel to the drainlumen and fluidically connected to the balloon interior through the atleast one inflation port, the at least one inflation lumen shaped toinflate the balloon interior with the inflation fluid, and a drainageport fluidically connecting the balloon interior to the drain lumen. Thehollow stretch valve is coaxially disposed in the drain lumen and shapedto permit fluid to pass therethrough, has a distal sliding portionslidably disposed within the drain lumen, is positioned in the drainlumen such that, in a steady state, the stretch valve prevents theinflation fluid from passing through the drainage port, and, in astretched state when the proximal catheter end is stretched, the distalsliding portion slides within the drain lumen to permit the inflationfluid to pass through the drainage port and into the drain lumen.

With the objects of the invention in view, there is also provided asafety catheter for draining a given fluid includes a hollow stretchvalve and a flexible, multi-lumen, balloon drainage catheter having aproximal catheter end, a balloon defining a balloon interior to beinflated with an inflation fluid, a drain lumen. and a balloon drainageport fluidically connecting the balloon interior to the drain lumen. Thehollow stretch valve is shaped to permit the given fluid to passtherethrough and is positioned in the drain lumen to at least partiallyslide therein such that, in a steady state, the stretch valve preventsthe inflation fluid from passing through the drainage port, and, in astretched state when the proximal catheter end is stretched, the distalsliding portion slides within the drain lumen to permit the inflationfluid to pass through the drainage port and into the drain lumen.

In accordance with another feature of the invention, the drainage portfluidically connects at least one of the balloon interior and the atleast one inflation lumen to the drain lumen.

In accordance with a further feature of the invention, the stretch valvehas a sliding portion and a stable portion, the sliding portion beingslidably disposed within the drain lumen at the drainage port such that,in the stretched state, the sliding portion slides within the drainlumen to permit the inflation fluid to pass through the drainage port.

In accordance with an added feature of the invention, the balloon has adistal balloon end and a proximal balloon end and the stretched stateoccurs when at least one of the distal and proximal balloon ends ismoved in a direction away from the other of the distal and proximalballoon ends.

In accordance with an additional feature of the invention, the stretchvalve has the stretched state at a pull force applied to the proximalshaft portion of between at least one of approximately 1 pound andapproximately 15 pounds, approximately 1 pound and approximately 5pounds, and approximately 1.5 pounds and approximately 2 pounds.

In accordance with yet another feature of the invention, the stretchvalve meets the stretched state and thereby deflates the inflated hollowballoon when at least one of the balloon portion is inflated with afluid and a pull force of greater than approximately 15 pounds isapplied to the proximal shaft portion, the balloon portion is inflatedwith a fluid and a pull force of greater than approximately 5 pounds isapplied to the proximal shaft portion, and the balloon portion isinflated with a fluid and a pull force of greater than approximately 2pounds is applied to the proximal shaft portion.

In accordance with yet a further feature of the invention, the stretchvalve has a proximal valve end opposite the distal sliding portion and afixed portion fixedly connected within the drain lumen adjacent theproximal valve end.

In accordance with yet an added feature of the invention, the proximalvalve end of the stretch valve is the fixed portion fixedly connectedwithin the drain lumen.

In accordance with yet an additional feature of the invention, thedrainage port is a plurality of drainage ports each fluidicallyconnecting the balloon interior to the drain lumen.

In accordance with again another feature of the invention, the drainageport is a plurality of drainage ports each fluidically connecting atleast one of the balloon interior and the at least one inflation lumento the drain lumen.

In accordance with again a further feature of the invention, thedrainage catheter has at least one inflation lumen fluidically connectedto the balloon interior through at least one inflation port and shapedto convey the inflation fluid thereto and therefrom.

In accordance with again an added feature of the invention, the drainagecatheter has a shaft outer diameter and the balloon is inflatableoutwardly to a diameter greater than the outer diameter of the shaft.

In accordance with again an additional feature of the invention, thestretch valve has a distal sliding portion slidably disposed in thedrain lumen, a proximal valve end opposite the distal sliding portion,and a fixed portion fixedly connected within the drain lumen adjacentthe proximal valve end.

In accordance with a concomitant feature of the invention, the drainageport is a plurality of drainage ports each fluidically connecting atleast one of the balloon interior and the at least one inflation lumento the drain lumen and the stretch valve, in the steady state, ispositioned in the drain lumen to prevent fluid from passing through theplurality of drainage ports, and, in the stretched state, the distalsliding portion slides within the drain lumen to permit the inflationfluid to pass through the plurality of drainage ports.

The low-pressure balloon catheter of the present invention preventsinjury by having the balloon automatically deflate before an injury canoccur, for example, when being forced to withdraw from the bladder orbeing forced to inflate within a urethra. The stretch valve ballooncatheter of the present invention prevents injury by having the balloonautomatically deflate before an injury can occur, for example, whenbeing forced to withdraw from the bladder prior to physician-scheduledmanual deflation. While the catheters of the present invention makes ita safer device for urinary drainage, the present invention can also beused for any procedures in which balloons are used to occlude cavities.Examples of these procedures include coronary artery vessels andperipheral vascular vessels, such as the aorta and extremity vessels.Balloon dilations of other lumens, such as ureters and the esophagus,are also candidates for use of the catheter of the present invention.Further, the mechanism of pressure release can be used for any fluid orair-filled device such as tissue expanders, percutaneous devices, andthe like.

Some of the embodiments of the present invention utilize a valve (e.g.,a slit valve or a stretch valve) that permits reuse when utilized. Withembodiments having no such valves, the invention is a single usecatheter after deflation occurs. Although deflation of such a single-usecatheter renders it useless, the act of immediate deflation protects thepatient from serious harm and the cost of replacing a catheter isminimal as compared to the significant cost of treating catheter-inducedinjury. Prevention of such injuries is becoming more and more importantbecause the injuries are commonplace. The increase occurs for a numberof reasons. First, a greater percentage of the population is aging.Second, there is a current trend to use less-skilled health carepersonnel to perform more procedures and to be responsible fortreatment, both of which save the hospitals and doctors money. Theshortage of nursing professionals (e.g., R.N.s) exacerbates this trend.The present tendency is to use nursing professionals for more functions,such as administration and delivery of medications. This leaves only theleast-skilled technicians with the task of taking vital signs andinserting catheters. Under such circumstances, more injuries are likelyand do, in fact, occur. Lastly, catheter-related complications arebecoming more severe due to the increased use of anticoagulationmedication, such as PLAVIX®, that is frequently prescribed in treatingcardiovascular disease.

Yet another possible complication arising from the standard Foleycatheter is that the balloon will not deflate even when the deflationmechanism is activated. This situation can occur, for example, becausethe wrong fluid is used to inflate the balloon or when a fluid, such assaline, crystallizes, which happens occasionally. Sometimes, the abilityto deflate the catheter is interrupted because the drainage channel thatis used to deflate the balloon becomes obstructed, which is common ifthe catheter is left in place too long. Remedy of such a scenarioinvolves an invasive procedure, which includes threading a needle orother sharp object somewhere through the body cavity to puncture theballoon and, thus, dislodge the catheter. This procedure is notdesirable and is to be avoided if possible. Yet another possiblecomplication can occur when the patient has a stricture, i.e., scartissue in the urethra that impedes the passage of the catheter. When atechnician is faced with a stricture, it seems to the technician thatthe catheter is no longer moving towards the bladder. Consequently, thetechnician uses excessive force to push the catheter into the bladder,thereby causing a tear that creates its own lumen into the penile andprostatic tissue. As is self-evident, this situation is accompanied bysignificant bleeding and the need for additional corrective proceduresand surgery.

With the low-pressure or valved, auto-deflating balloons of the presentinvention, the technician, nurse, or doctor merely needs to pull on thecatheter to cause the catheter to automatically deflate, thus sparingthe patient from any additional surgical procedures.

The added benefit of the present invention is not just for safety,significant financial benefits arise as well. It is believed thatcatheter-induced injuries are much more common than public documentationsuggests. Catheter-related trauma occurs no less that once a week in alarge metropolitan hospital. Usually, each incident not only increasesthe patient's hospital stay substantially, but also the expense of thestay. Each incident (which is usually not reimbursed by insurance) canincrease the cost to the hospital by thousands of dollars, even tens orhundreds of thousands of dollars. This is especially true when thepatient brings a personal injury action against the hospital,physician(s), and/or staff. And, when additional surgery is required torepair the catheter-induced injury, increased expense to the hospital isnot only substantial, if litigation occurs as a result of the injury,damages awarded to the patient can run into the millions of dollars. Thecatheters and methods of the present invention, therefore, provide asafer catheter that has the possibility of saving the medical industrybillions of dollars.

To prevent urethra tearing occurrences due to premature-improperinflation of the balloon and/or due to premature removal of an inflatedballoon, an exemplary embodiment of the invention of the instantapplication provides various balloon safety valves. Such valves areconfigured to release the inflation liquid from the balloon beforeinjury occurs.

The maximum stress that a typical urethra can take without tearingand/or breaking is known and is referred to as a maximum urethrapressure. It is also possible to calculate how much pressure is exertedupon the exterior of a balloon of a balloon catheter by measuring thepressure required to inflate the balloon. Knowing these two values, itis possible to construct a balloon that breaks rapidly and/or ceasesinflation if the maximum urethra pressure is exceeded.

For example, in a first exemplary embodiment, the balloon, which istypically some kind of rubber, silicone, elastomer, or plastic, can bemade with a breaking point that instantly deflates the balloon if thepressure in the balloon exceeds the maximum urethra pressure. It isacknowledged and accepted that, once the balloon breaks, this catheteris useless and must be discarded because the cost of patient injury faroutweighs the cost of the disposable catheter. Also, such a balloon islimited to inflation with a bio-safe fluid to prevent unwanted air/gasfrom entering the patient. If, however, air or other gas will not injurethe patient, the fluid can be air or another gas.

As an alternative to a one-use breaking safety valve, a multi-usepressure valve can be added to the balloon inflation lumen and can beset to open into the drainage lumen if the maximum urethra pressure isexceeded in the balloon or the balloon inflation lumen. Such a valve canbe located near or at the balloon inflation port, for example. Anycombination of the above embodiments is envisioned as well.

Another exemplary embodiment of the present invention provides thecatheter with a balloon that inflates with virtually no pressure. Asused herein, “virtually no pressure,” “zero-pressure” and “low-pressure”are used interchangeably and are defined as a range of pressure betweenapproximately standard atmospheric pressure and 0.3 atmospheres (5psig). This is in contrast to “high-pressure,” which is greater thanapproximately 1.5 atmospheres (22 psig). With such a configuration, thezero-pressure balloon can be deflated with virtually no force. As such,when the clinician attempts to inflate the zero-pressure balloon of thepresent invention within a urethra, the balloon simply does not inflate.Likewise, when the already inflated balloon within the bladder is forcedinto the urethra, such deflation needs virtually no pressure to collapsethe balloon to fit into the urethra. In both circumstances, injury tothe urethra is entirely prevented.

Further exemplary embodiments of the present invention that preventsurethra tearing occurrences due to premature removal of an inflatedballoon provides a balloon catheter with a stretch valve and methods formanufacturing and using such a valved catheter. In these variations, theinvention takes advantage of the fact that premature removal of theinflated balloon catheter requires stretching of the catheter at theproximal side of the balloon. The valved catheter can be configured witha release mechanism that is a function of elongation. With shortelongations, the balloon remains inflated however, when pulled beyond apreset limit, the valve automatically opens and drains the fluid fillingthe balloon. Some variations allow the balloon to even be refilled ifdeflation occurs without any injury. In either case, injury isprevented. Description of one exemplary embodiment herein in a way thatseparate from other exemplary embodiments is not to be construed meanthat the one embodiment mutually exclusive of the other exemplaryembodiments. The various exemplary embodiments of the safety cathetermentioned herein can be used separately and individually or they can beused together in any combination.

Although some variations are illustrated and described herein asembodied in a stretch valve balloon catheter and methods for producingand using such a catheter, they are, nevertheless, not intended to belimited to the details shown because various modifications andstructural changes may be made therein without departing from the spiritof the invention and within the scope and range of equivalents of theclaims. Additionally, well-known elements of exemplary embodiments ofthe invention will not be described in detail or will be omitted so asnot to obscure the relevant details of the invention.

Other features that are considered as characteristic for the inventionare set forth in the appended claims. As required, detailed embodimentsof the present invention are disclosed herein; however, it is to beunderstood that the disclosed embodiments are merely exemplary of theinvention, which can be embodied in various forms. Therefore, specificstructural and functional details disclosed herein are not to beinterpreted as limiting, but merely as a basis for the claims and as arepresentative basis for teaching one of ordinary skill in the art tovariously employ the present invention in virtually any appropriatelydetailed structure. Further, the terms and phrases used herein are notintended to be limiting; but rather, to provide an understandabledescription of the invention. While the specification concludes withclaims defining the features of the invention that are regarded asnovel, it is believed that the invention will be better understood froma consideration of the following description in conjunction with thedrawing figures, in which like reference numerals are carried forward.The figures of the drawings are not drawn to scale.

Before further disclosure and description, it is to be understood thatthe terminology used herein is for the purpose of describing particularembodiments only and is not intended to be limiting. The terms “a” or“an”, as used herein, are defined as one or more than one. The term“plurality,” as used herein, is defined as two or more than two. Theterm “another,” as used herein, is defined as at least a second or more.The terms “including” and/or “having,” as used herein, are defined ascomprising (i.e., open language). The term “coupled,” as used herein, isdefined as connected, although not necessarily directly, and notnecessarily mechanically.

As used herein, the term “about” or “approximately” applies to allnumeric values, whether or not explicitly indicated. These termsgenerally refer to a range of numbers that one of skill in the art wouldconsider equivalent to the recited values (i.e., having the samefunction or result). In many instances these terms may include numbersthat are rounded to the nearest significant figure. In this document,the term “longitudinal” should be understood to mean in a directioncorresponding to an elongated direction of the catheter. Lastly, theterm “proximal” refers to the end of the catheter closest to the personinserting the catheter and is usually that end of the catheter with ahub. The distal end of the catheter is the end furthest away from theperson inserting the catheter.

BRIEF DESCRIPTION OF THE DRAWINGS

In the following, the invention will be described in more detail byexemplary embodiments and the corresponding figures. By schematicillustrations that are not true to scale, the figures show differentexemplary embodiments of the invention.

FIG. 1 is a diagrammatic, fragmentary, longitudinal cross-sectional viewof a prior art catheter ideally placed in a urethra and a bladder of amale patient;

FIG. 2 is a fragmentary, enlarged, longitudinal cross-sectional view ofa distal portion of a first embodiment of a pressure-limiting ballooncatheter according to the invention;

FIG. 3 is a fragmentary, enlarged longitudinal cross-sectional view of aproximal portion of a second embodiment of a pressure-limiting ballooncatheter according to the invention;

FIG. 4 is a fragmentary, enlarged, cross-sectional view of a firstalternative configuration of the safety valve of FIG. 3;

FIG. 5 is a fragmentary, enlarged, cross-sectional view of a secondalternative configuration of the safety valve of FIG. 3;

FIG. 6 is a fragmentary, enlarged, cross-sectional view of a thirdalternative configuration of the safety valve of FIG. 3;

FIG. 7 is a fragmentary, further enlarged, cross-sectional view of thesafety valve of FIG. 6;

FIG. 8 is a fragmentary, further enlarged, cross-sectional view of afourth alternative configuration of the safety valve of FIG. 3;

FIG. 9 is a fragmentary, partially hidden, perspective view of anexemplary embodiment of a zero-pressure safety catheter according to theinvention;

FIG. 10 is a radial cross-sectional view of a portion of the catheter ofFIG. 9 at section line 10-10;

FIG. 11 is a process flow diagram of an exemplary method of forming azero-pressure balloon according to the invention;

FIG. 12 is a process flow diagram of an exemplary method of attaching azero-pressure balloon according to the invention;

FIG. 13 is a fragmentary, enlarged, perspective view of a distal portionof an exemplary embodiment of a zero-pressure catheter according to theinvention;

FIG. 14 is a radial cross-sectional view of a slit-valve portion of thecatheter of FIG. 13 at section line 14-14;

FIG. 15 is a radial cross-sectional view of an alternative embodiment ofa slit-valve portion of the catheter of FIG. 13 at section line 15-15;

FIG. 16 is a fragmentary, enlarged, partially cross-sectional andpartially perspective view of an everting balloon catheter according tothe invention in a correctly inserted position in the bladder;

FIG. 17 is a fragmentary, enlarged, partially cross-sectional andpartially perspective view of the catheter of FIG. 16 being pulleddistally out of the bladder and beginning its everting deflation;

FIG. 18 is a fragmentary, enlarged, partially cross-sectional view ofthe catheter of FIG. 16 with the everting deflation complete;

FIG. 19 is a fragmentary, enlarged, longitudinal cross-sectional view ofa balloon portion of a prior art urinary catheter in an uninflatedstate;

FIG. 20 is a fragmentary, enlarged, longitudinal cross-sectional view ofthe prior art urinary catheter of FIG. 19 in an inflated state within abladder;

FIG. 21 is a fragmentary, enlarged, longitudinal cross-sectional view ofa balloon portion of an exemplary embodiment of an automaticallydeflating, stretch valve urinary balloon catheter according to theinvention with the balloon in an uninflated state;

FIG. 22 is a fragmentary, enlarged, longitudinal cross-sectional view ofthe automatically deflating, stretch valve urinary balloon catheter ofFIG. 21 with the balloon in an inflated state and with the stretch valvein an unactuated state;

FIG. 23 is a fragmentary, enlarged, longitudinal cross-sectional view ofthe automatically deflating, stretch valve urinary balloon catheter ofFIG. 21 with the balloon in an inflated state and with the stretch valvein an actuated state;

FIG. 24 is a fragmentary, enlarged, longitudinal cross-sectional view ofa balloon portion of another exemplary embodiment of an automaticallydeflating, stretch valve urinary balloon catheter according to theinvention with the balloon in an uninflated state;

FIG. 25 is a fragmentary, enlarged, longitudinal cross-sectional view ofthe automatically deflating, stretch valve urinary balloon catheter ofFIG. 24 with the balloon in an inflated state and with the stretch valvein an unactuated state;

FIG. 26 is a fragmentary, enlarged, longitudinal cross-sectional view ofthe automatically deflating, stretch valve urinary balloon catheter ofFIG. 24 with the balloon in an inflated state and with the stretch valvein an actuated state;

FIG. 27 is a fragmentary, enlarged, longitudinal cross-sectional view ofa balloon portion of still another exemplary embodiment of anautomatically deflating, stretch valve urinary balloon catheteraccording to the invention with the balloon in an uninflated state;

FIG. 28 is a fragmentary, enlarged, longitudinal cross-sectional view ofthe automatically deflating, stretch valve urinary balloon catheter ofFIG. 27 with the balloon in an inflated state and with the stretch valvein an unactuated state;

FIG. 29 is a fragmentary, enlarged, longitudinal cross-sectional view ofthe automatically deflating, stretch valve urinary balloon catheter ofFIG. 27 with the balloon in an inflated state and with the stretch valvein an actuated state;

FIG. 30 is a fragmentary, enlarged, longitudinal cross-sectional view ofthe automatically deflating, stretch valve urinary balloon catheter ofFIG. 27;

FIG. 31 is a fragmentary, enlarged, longitudinal cross-sectional view ofthe automatically deflating, stretch valve urinary balloon catheter ofFIG. 27 turned ninety degrees counterclockwise when viewed from aproximal end thereof and with the stretch valve in an unactuated state;

FIG. 32 is a fragmentary, enlarged, longitudinal cross-sectional view ofthe automatically deflating, stretch valve urinary balloon catheter ofFIG. 27 turned ninety degrees counterclockwise when viewed from aproximal end thereof and with the stretch valve in an actuated state;

FIG. 33 is a fragmentary, enlarged, longitudinal cross-sectional view ofa balloon portion of yet another exemplary embodiment of anautomatically deflating, stretch valve urinary balloon catheteraccording to the invention with the balloon in a partially inflatedstate and the stretch valve in an unactuated state;

FIG. 34 is a fragmentary, enlarged, longitudinal cross-sectional view ofa balloon portion of yet a further exemplary embodiment of anautomatically deflating, stretch valve urinary balloon catheteraccording to the invention with the balloon in a partially inflatedstate and the stretch valve in an unactuated state

FIG. 35 is a fragmentary, enlarged, longitudinal cross-sectional view ofa balloon portion of still a further exemplary embodiment of anautomatically deflating, stretch valve urinary balloon catheteraccording to the invention with the balloon in a partially inflatedstate and the stretch valve in an unactuated state;

FIG. 36 is a fragmentary, enlarged, longitudinal cross-sectional view ofa balloon portion of an additional exemplary embodiment of anautomatically deflating, stretch valve urinary balloon catheteraccording to the invention with the balloon in a partially inflatedstate and the stretch valve in an unactuated state;

FIG. 37 is a fragmentary, enlarged, longitudinal cross-sectional view ofa balloon portion of another exemplary embodiment of an automaticallydeflating, stretch valve urinary balloon catheter according to theinvention with the balloon in a partially inflated state and the stretchvalve in an unactuated state;

FIG. 38 is a fragmentary, enlarged, longitudinal cross-sectional view ofa balloon portion of still another exemplary embodiment of anautomatically deflating, stretch valve urinary balloon catheteraccording to the invention with the balloon in a partially inflatedstate and the stretch valve in an unactuated state;

FIG. 39 is a flow chart of exemplary embodiments of processes for makinga catheter according to the invention;

FIG. 40 is a flow chart of exemplary embodiments of other processes formaking a catheter according to the invention; and

FIG. 41 is a flow chart of exemplary embodiments of further processesfor making a catheter according to the invention.

DETAILED DESCRIPTION OF THE EXEMPLARY EMBODIMENTS

While the specification concludes with claims defining the features ofthe invention that are regarded as novel, it is believed that theinvention will be better understood from a consideration of thefollowing description in conjunction with the drawing figures, in whichlike reference numerals are carried forward.

Herein various embodiment of the present invention are described. Inmany of the different embodiments, features are similar. Therefore, toavoid redundancy, repetitive description of these similar features maynot be made in some circumstances. It shall be understood, however, thatdescription of a first-appearing feature applies to the later describedsimilar feature and each respective description, therefore, is to beincorporated therein without such repetition.

Referring now to the figures of the drawings in detail and first,particularly to FIG. 2 thereof, there is shown a first embodiment of apressure-limiting balloon catheter 100 that does not inflate past thetearing limit of a lumen in which the catheter 100 is placed, forexample, in the urethra.

To prevent occurrences of urethra tearing due to premature-improperinflation of the balloon and/or due to premature removal of an inflatedballoon, the invention of the instant application provides the balloon110 with a balloon safety valve 112. As set forth above, in a balloon 3of a conventional catheter (see reference numerals 1 to 5 in FIG. 1),the high-pressure balloon 3 is fixed to the outer surface of the fluiddrainage lumen 120 (not shown in FIG. 1) and is not intended to beremoved therefrom or to burst thereon unless an extraordinary amount ofinflation occurs. Such a tearing event is not supposed to occur underany circumstances during use with a patient. If such an event happens,the material of the balloon 3 will open at a random location, based uponthe microscopic fractures or weaknesses in the material itself, and riskserious damage to the patient associated with the bursting, as well as arisk of balloon fragmentation, which could leave one or more pieces ofthe balloon 3 inside the patient after removal of the catheter 1.

In contrast to such conventional devices, the balloon 110 of the presentinvention is created specifically to tear when a predefined pressureexists in or is exerted on the balloon 110. The controlled tear willoccur because the balloon safety valve 112 is present. Conventionalballoons have constant balloon wall thicknesses (before inflation). Incontrast thereto, the balloon safety valve 112 in the first embodimentis a defined reduction in balloon wall thickness. This reduction createsa breaking point or selected breaking points at which the balloon 110 isintended specifically to break when a predefined force exists in or isimparted on the balloon 110. Because the balloon 110 is made of amaterial having a known tearing constant—dependent upon the thicknessthereof (which is determined experimentally for different thicknesses ofa given material prior to use in a patient), the balloon safety valve112 of the present invention for urethra applications is matched tobreak when the pressure inside or exerted on the balloon 110 approachesthe maximum urethra pressure.

In the embodiment shown in FIG. 2, a decreased thickness is formed as afirst semi-circumferential groove 114 near a proximal end of the balloon110 and/or as a second semi-circumferential groove 116 near a distal endof the balloon 110. The grooves 114, 116 can have any cross-sectionalshape, including, trapezoidal, triangular, square, or rectangle, forexample. Because rubber, plastic, and silicone materials tear well withthinner cuts, a relatively triangular shape or one with a narrow bottomcan be an exemplary configuration. To make sure that the entire balloon110 of the illustrated embodiment does not completely tear away from thefluid drainage lumen 120, both grooves 114, 116 do not extend around theentire circumference of the balloon 110. As shown to the left of theproximal groove 116 in FIG. 2, the groove 116 is not present on at leastan arc portion 118 of the circumference of the balloon 110. The arcportion is defined to be sufficiently large so that, when the catheter100 is removed from the patient, the balloon 110 cannot tear awayentirely from the catheter 100 (and create the disadvantageousfragmentation situation as set forth above). The illustrated balloonsafety valve 112 is, therefore, fashioned to keep the balloon 110 in onepiece after breaking and remain firmly connected to the catheter 100 toinsure that no piece of the balloon 110 will be left inside the patientafter actuation of the balloon safety valve 112. Alternatively, thegroove can be along the length of the balloon parallel to the axis ofthe catheter. This groove can be made by skiving the balloon afterattaching to the catheter or by skiving the balloon as it is formedduring extrusion or dip molding. In this embodiment, when the pressureexceeds a predetermined limit, the balloon splits along the groovewithout releasing fragments.

It is noted that the balloon 110 is inflated through an inflation lumen130 having a proximal opening, typically formed by one end of a luerconnector (see 260 in FIG. 3). The illustrated end is connected to anon-illustrated inflation device, for example, a distal end of a syringefor inflation of the balloon 110.

In this first embodiment, the balloon can be of an elastomer, rubber,silicone, or plastic, for example. Once the balloon breaks, the catheteris useless and must be discarded. Because the balloon 110 in thisembodiment will break inside the patient, it should be inflated with abio-safe fluid to prevent unwanted air, gas, or bio-unsafe fluid fromentering the patient. In certain circumstances where balloon cathetersare used, air or gas will not injure the patient if let out into thepatient's body cavity. In such circumstances, the inflating fluid can beair under pressure, for example.

Maximum urethra pressure can also be tailored to the individual patient.Based upon a urethral pressure-measuring device, the patient's maximumurethra pressure can be measured before the catheter 100 is placedtherein. A set of catheters 100 having different safety valve breakingconstants can be available to the physician and, after estimating orcalculating or knowing the patient's maximum urethra pressure, thephysician can select the catheter 100 having a safety valve breakingconstant slightly or substantially smaller than the patient's maximumurethra pressure. Accordingly, if the pressure in the balloon 110approaches the patient's maximum urethra pressure for any reason,whether it is due to over-inflation, improper placement, and/orpremature removal, the balloon 110 is guaranteed to break prior to thepatient's lumen (in particular, the patient's urethra) and, therefore,prior to causing injury.

A second embodiment of the one-use breaking safety valve of apressure-limiting balloon catheter 200 is shown in FIG. 3. The catheter200 has a fluid drainage lumen 220, a balloon inflation lumen 230, and asecondary lumen 240.

The fluid drainage lumen 220 is connected fluidically to the body cavity(i.e., the bladder 30) for draining fluid from the body cavity.

The secondary lumen 240 can be used for any purpose, for example, forhousing the radiation line that will supply energy to the radiation coil2. It can also be used for injecting fluid into any distal part of thecatheter 200 or even the body cavity itself.

The balloon inflation lumen 230 begins at a proximal end with aninflating connector 260 that, in an exemplary embodiment, is one part ofa luer connector. The balloon inflation lumen 230 continues through thebody of the catheter 200 all the way to the balloon 110 and isfluidically connected to the interior of the balloon 110.

Alternatively or additionally, the balloon safety valve is fluidicallyconnected to the balloon inflation lumen 230. In a second embodiment ofthe safety valve 212, the valve 212 is formed integrally with theballoon inflation lumen 230 and is set to open into the environment(instead of into the patient) if the maximum urethra pressure isexceeded in the balloon 110 or the balloon inflation lumen 230.Alternatively and not illustrated, the valve 212 is formed integrallywith the balloon inflation lumen 230 and is set to open into thedrainage lumen 220 if the maximum urethra pressure is exceeded in theballoon 110 or the balloon inflation lumen 230. A further alternativeincludes opening both into the environment and into the drainage lumen220. Because this safety valve 212 is located near or at the ballooninflation port 260 in this configuration, fluid used to inflate theballoon will not enter the patient when the valve 212 opens.

The safety valve 212 in the second embodiment can merely be a narrowingof the distance between the balloon inflation lumen 230 and the outersurface 250 of the catheter 220. In FIG. 3, the valve 212 has arectangular cross-section and extends away from the balloon inflationlumen 230. As shown in FIGS. 4, 5, and 6, respectively, thecross-section can be triangular (peaked or pyramidical inthree-dimensions), curved (circular or cylindrical in three-dimensions),or trapezoidal (frusto-conical or bar-shaped in three-dimensions). Thecross-sections are shown in FIGS. 3 to 7 with the narrowing emanatingfrom the balloon inflation lumen 230 outward. As an alternative, thenarrowing can begin on the outer surface of the catheter and extendinwards towards the balloon inflation lumen 230. A further alternativecan have the narrowing extend from both the inner lumen 230 and theouter surface of the catheter.

The cross-sections illustrated are merely exemplary. What is importantis that the thickness t between the bottom 213 of the valve 212 and theouter surface 250 of the catheter 220 in comparison to the thickness Tof the catheter body over the remainder of the balloon inflation lumen230. An enlarged view of this thickness comparison is illustrated inFIG. 7. As long as the thickness t is smaller than the thickness T(t<T), and as long as the force F_(b) required to break the balloon isgreater than the force F_(sv) required to break the portion 213 of thesafety valve 212 (Fb_(b)>F_(sv)), then the portion 213 of the safetyvalve 212 is virtually guaranteed to break every time pressure exertinga force F in the balloon inflation lumen 230 is greater than the forceF_(sv) required to break the safety valve (F_(sv)>F).

Based upon this analysis, the force F_(sv), required to break the safetyvalve can be tuned to whatever a patient needs or a physician desiresand different sized valves can be available for any procedure andprovided in the form of a kit. Whether a standard maximum urethrapressure is used or a patient-specific maximum urethra pressure ismeasured and used, experiments can be conducted prior to use on apatient on various catheter thicknesses t to determine the pressureneeded to break the portion 213 of the safety valve 212. For example,ten different maximum urethra pressures can be known as desirable setpoints and the thicknesses t can be varied such that pressure requiredto break the ten thicknesses correspond to the ten set point pressures.If, then, ten catheters are placed in such a kit, each having one of theten thicknesses, then the physician has a range of 10 maximum urethrapressure values to use with the patient.

Although FIGS. 3 to 7 show indentations into the wall of the catheter,the indentation can be in the form of a through-hole entirely throughthe wall of the catheter communicating with the outside of the catheterover which is placed a sleeve. Depending upon the pressure in theinflation lumen, fluid can leak through the hole and lift up the sleeveand leak to atmosphere therefrom. Pressure is controlled in thisembodiment by the modulus of the sleeve material. A harder sleeve thatfits snugly on the catheter will not allow leakage at low pressure.Alternatively, a softer rubbery sleeve would lift up easily to releasehigh pressure fluid.

The safety valve 212 of the second embodiment need not be confined tothe body of the catheter 200. Instead, the inflating connector 260 can,itself, be equipped with the pressure relief valve 212. Alternatively, anon-illustrated modular attachment containing the safety valve 212 canbe attached to the inflating connector 260. Such a modular valveattachment is removable and replaceable (such as through a conventionalluer or even a screw-threaded connection). Accordingly, as long as thecatheter 200 can still be used after the valve 212 actuates (breaks),the used modular valve attachment can be replaced with a new attachment.The converse is also true for reuse of the attachment if the catheter200 breaks and the valve of the attachment remains unbroken. Adownstream end of the modular valve attachment (e.g., shaped as part ofa luer connector) is attached removably to an upstream end of theinflating connector 260 and the upstream end of the modular valveattachment is to be connected to the balloon inflation device, which iscommonly a syringe. The upstream end of the modular valve attachment is,likewise, part of a luer connector for easy connection to standardmedical devices. In such a configuration, the safety valve 212, 312 ofthe present invention can be entirely separate from the catheter 200,300 and, therefore, form a retrofitting device for attachment to anyluer connector part present on conventional catheters.

As an alternative to the one-use breaking safety valve of the secondembodiment, a multi-use pressure valve can be used. This thirdembodiment of the pressure-limiting balloon catheter 300 is illustratedin FIG. 8. The catheter 300 can be the same as the catheter 200 in FIG.3 except for the portion illustrated in FIG. 8. Instead of having anarrowing thickness t of the lumen wall, the valve portion 313 extendsentirely to the environment (and/or into the drainage lumen 220).However, a one-way valve 314 (shown only diagrammatically in FIG. 8) isattached to the open end of the valve portion 313 and is secured to theouter surface 250 of the catheter 300 to close off the open end of thevalve portion 313. The one-way valve 314 can be secured directly to theouter surface 250 (e.g., with an adhesive), or a connector 315 (e.g., athreaded cap) can secure the one-way valve 314 to the open end of thevalve portion 313. Regardless of the configuration, the one-way valve314 includes a device that does not permit fluid from exiting the lumen230 until a given resistance R is overcome. This given resistance R canbe selectable by the physician depending upon the one-way valve that ischosen for use if a set of one-way valves having different resistances Rare available for use by the physician. Just like the second embodiment,the resistance R can be set to correspond to desired maximum urethrapressure values. Therefore, when used, the fluid exits the one-way valve314 into the environment well before the patient's maximum urethrapressure is exceeded by the balloon.

The one-way valve 314 can be a mechanical one-way valve. Additionally,the one-way valve 314 can be a material having a tear strengthcorresponding to a desired set of resistances R. The material can be afluid-tight fabric, a rubber, a plastic, or silicone different from thematerial making up the catheter. The material can even be a rubber,plastic, or silicone the same as the material making up the catheter buthaving a reduced thickness t than the thickness T of the catheter.Alternatively, the one-way valve 314 can be a slit valve. Variousexemplary embodiments of such a valve can be found in U.S. Pat. No.4,995,863 to Nichols et al., which is hereby incorporated herein byreference in its entirety.

It can also be appreciated that the pressure release (or relief) valvecan be a conventional pressure release valve comprised of a housing witha lumen, a ball, and a spring within the lumen wherein the springpresses the ball against a defined opening. When pressure on the ballexceeds the force of the spring, the ball moves away from the definedopening and fluid moves around the ball and vents to atmosphere. Bycontrolling tension on the spring, the pressure at which the valvereleases pressure can be controlled. It can also be appreciated that thepressure release valve can be coupled to a Luer connector, which can becoupled to a one-way check valve that can be used to inflate the balloonas is often used in conventional urinary drainage catheters.

Because the safety valve 212, 312 is located at the proximal end of thecatheter 200, 300, the distal end of the catheter 200, 300 can take theform of a distal end of a conventional balloon catheter 2, 3, 4, 5.Alternatively, the distal end shown in FIG. 2 can also be used forredundant over-pressure protection.

In another exemplary embodiment of the present invention, FIGS. 9 to 18illustrate alternatives to the elastomeric balloon described above. Inparticular, the above elastomeric balloon is replaced by a thin walled,pre-formed, fixed diameter balloon 1010 that inflates with virtually nopressure and withstands pressures between approximately 0.2 atmospheres(2.9 psi) and 0.5 atmospheres (7.35 psi), the latter of which isapproximately equal to the maximum urethra pressure, without anappreciable increase in diameter. Examples of such balloon materials andthicknesses are used in the medical field already, such as those used inangioplasty. Other exemplary materials can be those used in commercial(party) balloons, for example, MYLAR®, or similar materials such asnylon, PTA, PTFE, polyethylene and polyurethane, for example. In FIGS. 9and 13, the balloon 1010 is shown in a spherical shape. However, theballoon 1010 can be, for example, cylindrical with flat or conicallytapering ends.

The inflation balloon 1010 can be formed by heating a tubular materialwithin a mold or by heat-sealing thin sheets to one another (e.g., partyballoons have two sheets). One example of the relatively non-compliant,thin-walled balloon 1010 of the present invention is formed using ablow-molding process. In the blow-molding process, a thermoplasticmaterial such as nylon, polyurethane, or polycarbonate is extruded orformed into a hollow, tube-like shape (parison) and is subsequentlyheated and pressurized, usually with air, inside a hollow mold having ashape to form the final outer dimensions of the balloon. An example ofthe blow molded product is the common plastic soda or water bottlecontainers.

One exemplary, but not limiting, process to form the zero-pressureballoon of the present invention is described with respect to FIG. 11and includes, in Step 1110, cutting a relatively short piece of“parison” tubing that is formed using standard “air-mandrel” extrusiontechniques. In Step 1120, one end of the tubing is sealed. The centerportion of the tubing is placed in a hollow mold, leaving both endsextending outside of the mold in Step 1130. The center of the tubing isheated in Step 1140 with a hot stream of air through a small hole in thecenter of the mold for a few seconds to soften the tubing walls withinthe mold. The inside of the tubing is pressurized with a fluid, e.g.,air, in Step 1150 to stretch the tubing walls to conform to the insidedimensions of the mold. After a short cooling period, an additionalstretch of the formed balloon is done in Step 1160 by pulling on the(external) parison and, after a second “blowing” in the same mold inStep 1170, is used to create a very thin-walled balloon (much less than0.001 inches, typically, based upon the parison wall thickness and thefinal balloon diameter). The extra (unblown) parison tubing is then cutoff from both ends in Step 1180, leaving the thin walled, relativelysupple balloon and its “legs” to be mounted to the catheter as describedbelow.

This exemplary process can be used to create thin, non-compliantballoons for “angioplasty” of blood vessels at pressures exceeding 12atmospheres of pressure, for example. Although these pressures are notnecessary in the present application, it is witness to the fact thatvery strong thin-walled balloons can result from the above manufacturingprocess.

The present invention's thin, non-compliant zero-pressure balloon can beattached to the drainage catheter in a number of ways. In a firstexemplary attachment embodiment, reference is made to the process ofFIG. 12, the slit valve of FIG. 13, and the removable balloon of FIG.16.

In an exemplary embodiment, each of the distal and proximal legs of theballoon 1010 manufactured according to the process of FIG. 12 isattached to the distal end of the drainage catheter using standard(e.g., FDA-approved) cements or by heat fusing the two pieces together.The non-compliant, thin-walled balloon is dimensioned to envelop the“slit valves” shown, for example, in FIG. 13, as an exemplaryconfiguration of the invention. The balloon's thin walls allow foldingof the balloon without a significant increase in the catheter outerdiameter for ease in catheter insertion.

Exemplary embodiments of the internal balloon valve 1012 according tothe invention are illustrated in FIGS. 13, 14, and 15. This internalballoon valve 1012 is formed by cutting the wall of the drainage lumen1120 at the portion of the catheter within the balloon 1010. The slitcan be a single cut or a plurality of cuts. Some exemplary slit valvesother than those shown are described in U.S. Pat. No. 4,995,863 toNichols et al., all of which can be utilized for the present invention.The slit-opening pressure, therefore, can be regulated by adjusting thenumber, length and spacing of the slit(s) and the thickness of thedrainage lumen wall 1122. For example, the length and orientation of theslit(s) 1012 determines the pressure at which it/they will open anddrain the balloon inflation lumen 1130. In one particular embodimentshown in FIG. 15, the slits 1124 are cut through the elastomeric wallsin a way that results in a wedge-shaped cross-section. With this wedgeshape, fluid within the balloon can drain under pressure easily. Thewedge can be increasing or decreasing. With the former, the edges arechamfered towards one another from the central axis of the balloontoward the exterior thereof (e.g., illustrated in FIG. 15) and, with thelatter, the edges are chamfered towards one another from the exterior ofthe balloon toward the central axis.

In another exemplary embodiment, a non-illustrated, thin-walled slittedsleeve can be disposed over the portion of the drainage catheter wall1122 within the balloon 1010 and covering a throughbore fluidicallyconnecting the interior of the balloon 1010 to the interior of thedrainage lumen 1120. As such, pressure within the balloon 1010 will openthe slit(s) of the sleeve, thereby fluidically connecting the balloon1010 interior with the drainage lumen 1120 to transfer fluid in theballoon 1010 to the drainage lumen 1120. Each of these exemplary balloonconfigurations entirely prevents damage caused by improper inflation orpremature removal.

Alternatively, the balloon wall itself could be modified to burst at aparticular pressure to release the inflation media. This weakenedsection could be created by mechanical, chemical, or thermal treatmentfor example. Mechanical measures may be accomplished by scratching thesurface and, thus, thinning the balloon wall in a particular section tocause it to burst at a pre-determined pressure or actually slicing orpunching a hole in the wall and covering the area with a thinner, weakerfilm of material which will tear at a predetermined pressure lower thanthe rest of the balloon. Likewise, a chemical solvent could be appliedto create the same effect as the mechanical device above by makingchemical changes to the plastic molecular structure of the balloon walland, thereby, weakening a desired section of the balloon wall. Weakeninga section of the wall by heat to thereby re-orient its molecularstructure (much like softening by annealing) is also possible.Therefore, the preferential tearing of the balloon wall at apredetermined internal pressure can be effected in a number of ways asexemplified by, but not limited to, the methods described above.

A second exemplary, but not limiting, process to attach thezero-pressure balloon of the present invention to the safety catheter1600 of the present invention, which can be used with or without theslit valves, is described with respect to FIGS. 12 and 16 and includes,in Step 1210, assembling a first proximal leg 1620 of the balloon 1610over the distal end of the drainage catheter shaft 1630 in an “inverted”direction (open end toward the balloon interior as shown in FIG. 16).This inverted connection is accomplished with a mechanical release thatcan be formed, for example, merely by using the shape of the proximalleg 1620 of the balloon 1610 or by using a separate compression device,such as an elastic band, or by using adhesives that removably connectthe proximal leg 1620 to the drainage catheter shaft 1630. In acompression only example, the proximal balloon seal is, thereby, formedby the force of the “inverted” relatively non-compliant proximal leg1620 being extended over and around the distal end of the flexibledrainage catheter shaft 1630 by, for example, stretching the material ofthe drainage catheter shaft 1630 (e.g., silicone) to reduce its outerdiameter. The other, distal leg 1640 of the balloon 1610 can, then, beattached in Step 1220 using cements (as in the first example above) orby heat fusion. It is noted that, while attachment is shown anddescribed in an inverted orientation for the proximal leg 1620 and in anon-inverted orientation for the distal leg 1640, these are not the onlypossible orientations for each and can be assembled in any combinationof inverted and non-inverted orientations. For example, the distal leg1640 can, as the proximal leg 1620, be attached in an inverted directionnot illustrated in FIG. 16.

To further aid in balloon assembly and catheter deflation and insertion,the outer diameter of the catheter 1600 under the balloon 1610, as wellas the inner diameter of the distal balloon leg 1640, can be reduced ascompared with the outer diameter of the drainage catheter shaft 1630,which configuration is shown in FIGS. 16 to 19. The reduced-diameterportion of the catheter 1600 is referred herein as the distal tipportion 1650 and extends from the distal end of the drainage cathetershaft 1630 at least to the distal end of the distal balloon leg 1640. Asshown, the distal tip 5 (distal of the balloon 1610) also can have thesame reduced diameter (or can be reduced further or increased larger asdesired). Thus, if the outer diameter of the distal tip portion 1650 isreduced immediately distal of the proximal balloon seal 1620, anypredetermined pull force will stretch the catheter shaft 1630, therebyreducing the outer diameter of the catheter shaft 1630 at the proximalballoon seal and allowing the proximal balloon leg 1620 to slide or peeldistally and deflate the balloon quickly, at which time all fluid isreleased therefrom into the bladder or urethra, for example. It isenvisioned that the proximal balloon leg 1620 can be mounted with theballoon leg 1620 in a non-inverted or “straight” position if desiredwith similar results. However, in such a configuration, sliding of theproximal leg 1620 over the distal end of the catheter shaft 1630 may bemore resistant to a pulling force on the exposed proximal end of thecatheter shaft 1630 but the slight incursion of the balloon-fillingfluid can be used to lubricate this connection and, therefore, theresistance to pulling decreases.

With a zero-pressure configuration as described and referred to herein,the balloon 1010, 1610 is under zero-pressure or low pressure. Thus, theinflation device (e.g., a syringe) need not be configured to deliverpressure much above the low pressure range described above. Merepresence of the filling liquid in the balloon, makes the balloon largeenough to resist and prevent movement of the balloon into the urethraand out of the bladder without having an internal, high pressure. Assuch, when inserted improperly in the urethra, the balloon will simplynot inflate because there is no physical space for the balloon to expandand because the inflation pressure remains beneath the urethral damagingpressure threshold. If the inflation device is configured for lowpressure, even maximum delivered pressure to the balloon will beinsufficient to inflate the balloon within the urethra, therebypreventing any possibility of balloon inflation inside the urethra.

In the other case where the balloon is inflated properly within thebladder but the catheter is improperly removed out from the patientwithout deflating the balloon, safety devices of the invention preventtearing of the urethra upon exit. Any combination of the internalballoon valve 1012 (e.g., the slit valve of FIG. 13 formed through thewall of a portion of the drainage lumen 1120 located inside the balloon1010, 1610) and the removable proximal balloon seal 1620 can be used;one or both can be employed to provide the safety features of theinvention. In operation, when a predetermined inflation pressure isreached, the internal balloon valve 1012 opens and any fluid in theballoon 1010, 1610 is emptied through the drainage lumen 1120 into thebladder (distal) and/or the external drain bag (proximal), the latter ofwhich is not illustrated. As set forth above, the point at whichpressure causes the internal balloon valve 1012 to open is defined to beless than the pressure needed to damage the urethra when a fullyinflated prior-art balloon catheter is improperly removed as describedherein. In a low-pressure state, in which the balloon 1010, 1610 isfilled with a fluid (either liquid or gas), there is not enough pressureto force open the internal balloon valve 1012 and permit exit of thefluid out from the balloon 1010, 1610. In a higher-pressure state (belowurethra damage pressure), in contrast, pressure exerted on the fluid issufficient to open the internal balloon valve 1012, thus permitting thefluid to quickly drain out of the balloon 1010, 1610 and into thedrainage lumen 1120.

In a situation where the balloon 1010, 1610 is in the urethra andinflation is attempted, pressure exerted by the surrounding urethralwall on the inflating balloon 1010, 1610 will cause the internal balloonvalve 1012 to open up well before the balloon 1010, 1610 could inflate.Thus, the balloon inflation fluid will, instead of filling the balloon1010, 1610, exit directly into the drainage lumen 1120. In analternative embodiment, the fluid used can be colored to contrast withurine (or any other fluid that is envisioned to pass through thedrainage lumen). Thus, if the balloon 1010, 1610 is inserted only intothe urethra and inflation is attempted, the inflating fluid willimmediately exit into the drainage lumen and enter the exterior(non-illustrated) drain bag. Thus, within a few seconds, the technicianwill know if the balloon 1010, 1610 did not enter the bladder andinflate therein properly by seeing the colored inflation fluid in thedrain bag. In such a situation, the technician needs to only insert thecatheter further into the urethra and attempt inflation again. Theabsence of further colored inflation fluid in the drain bag indicatesthat correct balloon inflation occurred.

In the other situation where the balloon 1010, 1610 is inflated withinthe bladder and the catheter 100 is pulled out from the bladder withoutdeflating the balloon 1010, 1610, pressure exerted by the urethrovesicaljunction 11 upon the inflated balloon 1010, 1610 will cause the valve1012 to open up quickly and cause fluid flow into the drainage lumen1120 before injury occurs to the junction 11 or the urethra. If, in sucha situation, the catheter is also equipped with the removable balloonend (e.g., proximal end 1620), then, as the removable balloon end ispeeling off, the slit valve opens up to relieve pressure either beforeor at the same time the peeling off occurs. This allows the inflationfluid to exit even faster than if just the valve 1012 is present.

FIGS. 16 to 18 illustrate an exemplary embodiment of the inventivecatheter 1600 with the everting removable balloon 1610. These figuresillustrate the situation where the balloon 1610 is inflated within thebladder and, as indicated by the pull arrow, the catheter 1600 is pulledout from the bladder without deflating the balloon 1610. Here, thedistal seal 1640 of the balloon 1610 is fixed to the distal tip portion1650 of the catheter 1600, which tip 5 has a reduced outer diameter ascompared to the drainage catheter shaft 1630, and the proximal seal 1620is removably attached (e.g., with a compression seal) to the drainagecatheter shaft 1630. The pulling force causes the drainage cathetershaft 1630 to move in the proximal direction out of the urethra and,thereby, compress the proximal side of the inflated balloon 1610 againstthe urethrovesical junction 11. As the catheter shaft 1630 movesproximally, the force on the proximal seal 1620 increases until the seal1620 breaks free of the catheter shaft 1630, referred to herein as thebreakaway point. FIG. 17 illustrates the now partially inflated balloon1610 just after the breakaway point. Because the diameter of the distaltip portion 1650 is reduced in comparison to the distal end of thecatheter shaft 1630, a gap opens up between the inner diameter of theproximal seal portion of the balloon 1610 and the outer diameter of thedistal tip portion 1650. This gap allows the inflating fluid to exit theballoon 1610 quickly into one or both of the urethra and the bladderbefore injury occurs to the junction 11 or to the urethra. As thecentral portion of the balloon 1610 is still larger than the urethralopening of the junction 11, the friction and force imparted on theballoon 1610 causes the balloon 1610 to roll over itself, i.e., evert,until it is entirely everted as shown in FIG. 18. At this time, all ofthe inflating fluid is either in the urethra and/or in the bladder.

In an exemplary embodiment of the removable proximal balloon seal 1620,a pulling force in a range of 1 to 15 pounds will cause the proximalballoon seal 1620 to pull free and allow eversion of the balloon 1610,i.e., the breakaway point. In another exemplary embodiment, the range offorce required to meet the breakaway point is between 1 and 5 pounds, inparticular, between 1.5 and 2 pounds.

With regard to additional exemplary embodiments of self-deflating orautomatically deflating balloon catheters according to the invention,FIGS. 19 and 20 are provided to illustrate the construction andprocesses for manufacturing prior art urinary catheters, also referredto as Foley catheters. Although prior art urinary catheters are usedherein to assist in the understanding of the exemplary embodiments ofurinary balloon catheters according to the invention, neither are usedherein to imply that the invention is solely applicable to urinary-typecatheters. Instead, the technology described herein can be applied toany balloon catheter.

FIG. 19 shows the balloon portion of the prior art catheter 1900 withthe balloon in its uninflated state. An annular inner lumen wall 1910(red) defines therein a drainage lumen 1912. At one circumferentiallongitudinal extent about the inner lumen wall 1910, an inflation lumenwall 1920 (orange) defines an inflation lumen 1922 and a ballooninflation port 1924 fluidically connected to the inflation lumen 1922;in standard urinary catheters, there is only one inflation lumen 1922and one inflation port 1924. The views of FIGS. 19 and 20 show across-section through the inflation lumen 1922 and inflation port 1924.If the inflation lumen 1922 extended all of the way through the catheter1900 to its distal end (to the left of FIGS. 19 and 20), then theballoon could not inflate as all inflation liquid would exit the distalend. Therefore, in order to allow inflation of the balloon, a lumen plug1926 (black) closes the inflation lumen 1922 distal of the inflationport 1924. In this exemplary illustration, the lumen plug 1926 starts ata position distal of the inflation port 1924 at the inflation lumen1922.

About the inner lumen and inflation lumen walls 1910, 1920 around theinflation port 1924 is a tube of material that forms the ballooninterior wall 1930 (green). The tube forming the balloon interior wall1930 is fluid-tightly sealed against the respective inner walls 1910,1920 only at the proximal and distal ends of the tube. Accordingly, apocket is formed therebetween. An outer wall 1940 (yellow) covers all ofthe walls 1910, 1920, 1926, 1930 and does so in what has referred toherein as a fluid-tight manner, meaning that any fluid used to blow upthe balloon through the inflation lumen 1922 and the inflation port 1924will not exit the catheter 1900 through the fluid-tight connection. FIG.20 illustrates the fluid inflating the balloon (indicated with dashedarrows). Because at least the balloon interior wall 1930 and the outerwall 1940 are elastomeric, pressure exerted by the inflating fluid 2000against these walls will cause them to balloon outwards as, for example,shown in FIG. 20. When the non-illustrated proximal end of the catheter1900 is sealed with the fluid 2000 therein (e.g., with at least a partof a luer connector as shown in FIG. 3), the catheter 1900 will remainin the shape shown in FIG. 20.

As set forth above, the balloon 2010 of a urinary catheter should beinflated only when in the bladder 2020. FIG. 20 shows the catheter 1900correctly inflated in the bladder 2020 and then, if needed, pulledproximally so that the inflated balloon 2010 rests against andsubstantially seals off the urethra 2030 from the interior of thebladder 2020. “Substantially,” as used in this regard means that most orall of the urine in the bladder 2020 will drain through the drain lumen1912 and will not pass around the inflated balloon 2010 more than istypical and/or required for correctly implanted urinary catheters. It isknown that an insubstantial amount of urine will pass the balloon 2010and, advantageously, lubricate the urethra 2030 but will not leak outthe end of the urethra as muscles in the various anatomy of males andfemales will seal the end with sufficient force to prevent significantleakage.

Even though each of the walls is shown in different colors herein, thedifferent colors do not imply that the respective walls must be made ofdifferent materials. These colors are used merely for clarity purposesto show the individual parts of the prior art and inventive cathetersdescribed herein. As will be described in further detail below, most ofthe different colored walls actually are, in standard urinary catheters,made of the same material. Some of the biocompatible materials used forstandard Foley catheters include latex (natural or synthetic), siliconerubber, and thermoplastic elastomers (TPEs) including styrenic blockcopolymers, polyolefin blends, elastomeric alloys (TPE-v or TPV),thermoplastic polyurethanes, thermoplastic copolyester, andthermoplastic polyamides.

One exemplary process for creating the prior art urinary cathetersstarts with a dual lumen extrusion of latex. The dual lumen, therefore,already includes both the drainage lumen 1912 and the inflation lumen1922. Both lumen 1912, 1922, however, are extruded without obstructionand without radial ports. Therefore, in order to have the inflation port1924, a radial hole is created from the outside surface inwards to theinflation lumen. Sealing off of the distal end of the inflation lumen1922 is performed in a subsequent step. The tube making up the innerballoon wall 1930 is slid over the distal end of the multi-lumenextrusion 1910, 1920 to cover the inflation port and is fluid-tightlysealed to the inner multi-lumen extrusion at both ends of the tube butnot in the intermediate portion. This tube can be made of latex as welland, therefore, can be secured to the latex multi-lumen extrusion in anyknown way to bond latex in a fluid-tight manner. At this point, theentire sub-assembly is dipped into latex in its liquid form to createthe outer wall 1940. The latex is allowed to enter at least a portion ofthe distal end of the inflation lumen 1922 but not so far as to blockthe inflation port 1924. When the latex cures, the balloon 2010 is fluidtight and can only be fluidically connected to the environment throughthe non-illustrated, proximal-most opening of the inflation port, whichis fluidically connected to the inflation lumen 1922. In this process,the inner wall 1910, the inflation lumen wall 1920, the plug 1926, theballoon inner wall 1930, and the outer wall 1940 are all made of thesame latex material and, therefore, together, form a very securelywater-tight balloon 2010.

As set forth above, all prior art balloon catheters are designed todeflate only when actively deflated, either by a syringe similar to theone that inflated it or by surgery after the physician diagnoses theballoon as not being able to deflate, in which circumstance, a procedureto pop the balloon surgically is required.

Described above are various embodiments of self-deflating orautomatically deflating catheters according to the invention. FIGS. 21to 33 illustrate automatically deflating, stretch-valve ballooncatheters in still other exemplary embodiments of the present invention.FIGS. 21 to 23 show a first exemplary embodiment of a stretch-valveballoon catheter 2100 according to the invention, FIG. 21 illustratingthe balloon portion of the inventive catheter 2100 with the balloon inits uninflated state. An annular inner lumen wall 2110 (red) definestherein a drainage lumen 2112. At one or more circumferentiallongitudinal extents about the inner lumen wall 2110, an inflation lumenwall 2120 (orange) defines an inflation lumen 2122 and a ballooninflation port 2124 fluidically connected to the inflation lumen 2122;in the inventive catheter, there can be more than one inflation lumen2122 and corresponding inflation port 2124 even though only one is shownherein. Accordingly, the views of FIGS. 21 to 23 show a cross-sectionthrough the single inflation lumen 2122 and single inflation port 2124.A lumen plug 2126 (black) closes the inflation lumen 2122 distal of theinflation port 2124. In this exemplary illustration, the lumen plug 2126starts at a position distal of the inflation port 2124 at the inflationlumen 2122. This configuration is only exemplary and can start at theinflation port 2124 or anywhere distal thereof.

About the inner lumen and inflation lumen walls 2110, 2120 around theinflation port 2124 is a tube of material that forms the ballooninterior wall 2130 (green). The tube of the balloon interior wall 2130is fluid-tightly sealed against the respective inner walls 2110, 2120only at the proximal and distal ends of the tube. Accordingly, a pocketis formed therebetween. An outer wall 2140 (yellow) covers all of thewalls 2110, 2120, 2126, 2130 in a fluid-tight manner. FIG. 21illustrates the fluid about to inflate the balloon (indicated withdashed arrows). Because at least the balloon interior wall 2130 and theouter wall 2140 are elastomeric, pressure exerted by the inflating fluid2200 against these walls will cause them to balloon outwards as, forexample, shown in FIG. 22. When the non-illustrated proximal end of thecatheter 2100 is sealed with the fluid 2200 therein (e.g., with at leasta part of a luer connector as shown in FIG. 3), the catheter 2100 willremain in the shape shown in FIG. 22.

FIG. 22 shows the catheter 2100 correctly inflated in the bladder 2020and then, if needed, pulled proximally so that the inflated balloon 2210rests against and substantially seals off the urethra 2030 from theinterior of the bladder 2020.

The stretch-valve of the exemplary embodiment of FIGS. 21 to 23 hasthree different aspects. The first is a hollow, stretch-valve tube 2220that is disposed in the inflation lumen 2122 to not hinder inflation ofthe balloon 2210 with the fluid 2200. While the diameter of thestretch-valve tube 2220 can be any size that accommodates unhinderedfluid flow through the inflation lumen 2122, one exemplary innerdiameter of the stretch-valve tube 2220 is substantially equal to thediameter of the inflation lumen 2122 and the outer diameter of thestretch-valve tube 2220 is just slightly larger than the diameter of theinflation lumen 2122 (e.g., the wall thickness of the tube can bebetween 0.05 mm and 0.2 mm). The proximal end of the stretch-valve tube2220 in this exemplary embodiment is proximal of a proximal end of theballoon inner wall 2130. The distal end of the stretch-valve tube 2220is somewhere near the proximal end of the balloon inner wall 2130; thedistal end can be proximal, at, or distal to the proximal end of theballoon inner wall 2130 and selection of this position is dependent uponthe amount of stretch S required to actuate the stretch-valve of theinventive catheter 2100 as described below. In FIG. 22, the distal endof the stretch-valve tube 2220 is shown at the proximal end of theballoon inner wall 2130. Two ports are formed proximal of the balloon2210. A proximal port (purple) 2150 is formed through the outer wall2140 and through the inflation lumen wall 2020 overlapping at least aportion of the proximal end of the stretch-valve tube 2220. In thismanner, a portion of the outer surface of the proximal end of thestretch-valve tube 2220 at the proximal port 2150 is exposed to theenvironment but there is no fluid communication with the inflation lumen2122 and the proximal port 2150. A distal port (white) 2160 is formedthrough the outer wall 2140 and through the inflation lumen wall 2020overlapping at least a portion of the distal end of the stretch-valvetube 2220. In this manner, a portion of the outer surface of the distalend of the stretch-valve tube 2220 at the distal port 2160 is exposed tothe environment but there is no fluid communication from the inflationlumen 2122 to the distal port 2160. To secure the stretch-valve tube2220 in the catheter 2100, the proximal port 2150 is filled with amaterial that fixes the proximal end of the stretch-valve tube 2220 toat least one of the outer wall 2140 and the inflation lumen wall 2020.In one exemplary embodiment, an adhesive bonds the proximal end of thestretch-valve tube 2220 to both the outer wall 2140 and the inflationlumen wall 2120.

In such a configuration, therefore, any proximal movement of thecatheter 2100 at or proximal of the proximal port 2150 will also movethe stretch-valve tube 2220 proximally; in other words, the distal endof the stretch-valve tube 2220 can slide S within the inflation lumen2122 in a proximal direction. FIG. 23 illustrates how the slide-valve ofthe invention operates when the proximal end of the catheter 2100 ispulled with a force that is no greater than just before injury wouldoccur to the urethrovesical junction or the urethra if the catheter 2100was still inflated when the force was imparted. In an exemplaryembodiment of the stretch valve of FIGS. 21 to 23, a pulling force in arange of 1 to 15 pounds will cause the stretch-valve tube 2220 to slideproximally S to place the distal end of the stretch-valve tube 2220 justproximal of the distal port 2160, i.e., the deflation point of thestretch-valve shown in FIG. 23. In another exemplary embodiment, therange of force required to meet the deflation point is between 1 and 5pounds, in particular, between 1.5 and 2 pounds.

As can be seen in FIG. 23, when the deflation point of the stretch-valveis reached, the interior of the balloon 2210 becomes fluidicallyconnected to the distal port 2160. Because the distal port 2160 is opento the environment (e.g., the interior of the bladder 2020) and due tothe fact that the bladder is relatively unpressurized as compared to theballoon 2210, all internal pressure is released from the balloon 2210 toeject the inflating fluid 2200 into the bladder 2020 (depicted by dashedarrows), thereby causing the balloon 2210 to deflate rapidly (depictedby solid opposing arrows). It is noted that the distance X (see FIG. 22)between the inflation port 2124 and the distal port 2160 directlyimpacts the rate at which the balloon 2120 deflates. As such, reducingthis distance X will increase the speed at which the balloon 2210deflates. Also, the cross-sectional areas of the inflation port 2124,the inflation lumen 2122, and the distal port 2160 directly impact therate at which the balloon 2220 deflates. Further, any changes indirection of the fluid can hinder the rate at which the balloondeflates. One way to speed up deflation can be to shape the distal port2160 in the form of a non-illustrated funnel outwardly expanding fromthe inflation lumen 2122. Another way to speed up deflation is to havetwo or more inflation lumens 2122 about the circumference of the innerlumen wall 2110 and to have corresponding sets of a stretch-valve tube2220, a proximal port 2150, and a distal port 2160 for each inflationlumen 2122.

Still another possibility for rapidly deflating an inflated balloon isto drain the fluid 2200 into the drain lumen 2112 instead of thebladder. This exemplary embodiment is illustrated in FIGS. 24 to 26.FIG. 24 illustrates the balloon portion of the inventive catheter 2400with the balloon in its uninflated state. An annular inner lumen wall2410 (red) defines therein a drainage lumen 2412. At one or morecircumferential longitudinal extents about the inner lumen wall 2410, aninflation lumen wall 2420 (orange) defines an inflation lumen 2422 and aballoon inflation port 2424 fluidically connected to the inflation lumen2422; in the inventive catheter, there can be more than one inflationlumen 2422 and corresponding inflation port 2424 even though only one isshown herein. Accordingly, the views of FIGS. 24 to 26 show across-section through the single inflation lumen 2422 and singleinflation port 2424. A lumen plug 2426 (black) closes the inflationlumen 2422 distal of the inflation port 2424. In this exemplaryillustration, the lumen plug 2426 starts at a position distal of theinflation port 2424 at the inflation lumen 2422. This configuration isonly exemplary and can start at the inflation port 2424 or anywheredistal thereof.

About the inner lumen and inflation lumen walls 2410, 2420 around theinflation port 2424 is a tube of material that forms the ballooninterior wall 2430 (green). The tube of the balloon interior wall 2430is fluid-tightly sealed against the respective inner walls 2410, 2420only at the proximal and distal ends of the tube. Accordingly, a pocketis formed therebetween. An outer wall 2440 (yellow) covers all of thewalls 2410, 2420, 2426, 2430 in a fluid-tight manner. FIG. 24illustrates the fluid about to inflate the balloon (indicated withdashed arrows). Because at least the balloon interior wall 2430 and theouter wall 2440 are elastomeric, pressure exerted by the inflating fluid2200 against these walls will cause them to balloon outwards as, forexample, shown in FIG. 25. When the non-illustrated proximal end of thecatheter 2400 is sealed with the fluid 2200 therein (e.g., with at leasta part of a luer connector as shown in FIG. 3), the catheter 2400 willremain in the shape shown in FIG. 25.

FIG. 25 shows the catheter 2400 correctly inflated in the bladder 2020and then, if needed, pulled proximally so that the inflated balloon 2510rests against and substantially seals off the urethra 2030 from theinterior of the bladder 2020.

The stretch-valve of the exemplary embodiment of FIGS. 24 to 26 hasthree different aspects. The first is a hollow, stretch-valve tube 2520that is disposed in the inflation lumen 2422 to not hinder inflation ofthe balloon 2510 with the fluid 2200. While the diameter of thestretch-valve tube 2520 can be any size that accommodates unhinderedfluid flow through the inflation lumen 2422, one exemplary innerdiameter of the stretch-valve tube 2520 is substantially equal to thediameter of the inflation lumen 2422 and the outer diameter of thestretch-valve tube 2520 is just slightly larger than the diameter of theinflation lumen 2122 (e.g., the wall thickness of the tube can bebetween 0.05 mm and 0.2 mm). The proximal end of the stretch-valve tube2520 in this exemplary embodiment is disposed proximal of a proximal endof the balloon inner wall 2430. The distal end of the stretch-valve tube2520 is somewhere near the proximal end of the balloon inner wall 2430;the distal end can be proximal, at, or distal to the proximal end of theballoon inner wall 2430 and selection of this position is dependent uponthe amount of stretch S required to actuate the stretch-valve of theinventive catheter 2400 as described below. In the exemplary embodimentof FIG. 25, the distal end of the stretch-valve tube 2520 is shown atproximal end of the balloon inner wall 2430. Two ports are formed, oneproximal of the balloon 2510 and one proximal of the inflation port2424. A proximal port (purple) 2450 is formed through the outer wall2440 and through the inflation lumen wall 2420 to overlap at least aportion of the proximal end of the stretch-valve tube 2520. In thismanner, a portion of the outer surface of the proximal end of thestretch-valve tube 2520 at the proximal port 2450 is exposed to theenvironment but there is no fluid communication between the inflationlumen 2422 and the proximal port 2450. A distal port (white) 2460 isformed through the inner lumen wall 2410 anywhere proximal of theinflation port 2424 to overlap a least a portion of the distal end ofthe stretch-valve tube 2520. In this manner, a portion of the outersurface of the distal end of the stretch-valve tube 2520 at the distalport 2460 is exposed to the drainage lumen 2412 but there is no fluidcommunication between the inflation lumen 2422 and the distal port 2460.To secure the stretch-valve tube 2520 in the catheter 2400, the proximalport 2450 is filled with a material that fixes the proximal end of thestretch-valve tube 2520 to at least one of the outer wall 2440 and theinflation lumen wall 2420. In one exemplary embodiment, an adhesivebonds the proximal end of the stretch-valve tube 2520 to both the outerwall 2440 and the inflation lumen wall 2420.

In such a configuration, therefore, any proximal movement of thecatheter 2400 at or proximal to the proximal port 2450 will also movethe stretch-valve tube 2520 proximally; in other words, the distal endof the stretch-valve tube 2520 can slide S within the inflation lumen2422 in a proximal direction. FIG. 26 illustrates how the slide-valve ofthe invention operates when the proximal end of the catheter 2400 ispulled to a force that is no greater than just before injury would occurto the urethrovesical junction or the urethra if the catheter 2400 wasstill inflated when the force was imparted. In an exemplary embodimentof the stretch valve of FIGS. 24 to 26, a pulling force in a range of 1to 15 pounds will cause the stretch-valve tube 2520 to slide proximallyS to place the distal end of the stretch-valve tube 2520 just proximalof the distal port 2460, i.e., the deflation point of the stretch-valveshown in FIG. 26. In another exemplary embodiment, the range of forcerequired to meet the deflation point is between 1 and 5 pounds, inparticular, between 1.5 and 2 pounds.

As can be seen in FIG. 26, when the deflation point of the stretch-valveis reached, the interior of the balloon 2510 becomes fluidicallyconnected to the distal port 2460. Because the distal port 2460 is opento the drainage lumen 2412 (which is open the interior of the bladder2020 and the non-illustrated, proximal drainage bag) and due to the factthat the bladder is relatively unpressurized as compared to the balloon2510, all internal pressure is released from the balloon 2510 to ejectthe inflating fluid 2200 into the drainage lumen 2412 (depicted bydashed arrows), thereby causing the balloon 2510 to deflate rapidly(depicted by solid opposing arrows). Again, it is noted that thedistance X between the inflation port 2424 and the distal port 2460 (seeFIG. 25) directly impacts the rate at which the balloon 2510 deflates.As such, having this distance X be smaller will increase the speed atwhich the balloon 2510 deflates. Also, the cross-sectional areas of theinflation port 2424, the inflation lumen 2422, and the distal port 2460directly impact the rate at which the balloon 2120 deflates. Further,any changes in direction of the fluid can hinder the rate at which theballoon deflates. One way to speed up deflation can be to shape thedistal port 2460 in the form of a funnel outwardly expanding from theinflation lumen 2422. Another way to speed up deflation can be to havetwo or more inflation lumens 2422 about the circumference of the innerlumen wall 2410 and to have corresponding sets of a stretch-valve tube2520, a proximal port 2450, and a distal port 2460 for each inflationlumen 2422.

Yet another exemplary embodiment that is not illustrated herein is tocombine both of the embodiments of FIGS. 21 to 23 and 24 to 26 to havethe fluid 2200 drain out from both of the distal ports 2160, 2460 intoboth the bladder 2020 and the drain lumen 2112, respectively.

Still another possibility for rapidly deflating an inflated balloon isto drain the fluid 2200 directly into the drain lumen 2712 in a straightline without any longitudinal travel X. This exemplary embodiment isillustrated in FIGS. 27 to 29. FIG. 27 illustrates the balloon portionof the inventive catheter 2700 with the balloon in its uninflated state.An annular inner lumen wall 2710 (red) defines therein a drainage lumen2712. At one or more circumferential longitudinal extents about theinner lumen wall 2710, an inflation lumen wall 2720 (orange) defines aninflation lumen 2722 and a balloon inflation port 2724 fluidicallyconnected to the inflation lumen 2722; in the inventive catheter, therecan be more than one inflation lumen 2722 and corresponding inflationport 2724 even though only one is shown herein. Accordingly, the viewsof FIGS. 27 to 29 show a cross-section through the single inflationlumen 2722 and single inflation port 2724. A lumen plug 2726 (black)closes the inflation lumen 2722 distal of the inflation port 2724. Inthis exemplary illustration, the lumen plug 2726 starts at a positiondistal of the inflation port 2724 at the inflation lumen 2722. Thisconfiguration is only exemplary and can start at the inflation port 2724or anywhere distal thereof.

About the inner lumen and inflation lumen walls 2710, 2720 around theinflation port 2724 is a tube of material that forms the ballooninterior wall 2730 (green). The tube of the balloon interior wall 2730is fluid-tightly sealed against the respective inner walls 2710, 2720only at the proximal and distal ends of the tube. Accordingly, a pocketis formed therebetween. An outer wall 2740 (yellow) covers all of thewalls 2710, 2720, 2726, 2730 in a fluid-tight manner. FIG. 27illustrates the fluid about to inflate the balloon (indicated withdashed arrows). Because at least the balloon interior wall 2730 and theouter wall 2740 are elastomeric, pressure exerted by the inflating fluid2200 against these walls will cause them to balloon outwards as, forexample, shown in FIG. 28. When the non-illustrated proximal end of thecatheter 2700 is sealed with the fluid 2200 therein (e.g., with at leasta part of a luer connector as shown in FIG. 3), the catheter 2700 willremain in the shape shown in FIG. 28.

FIG. 28 shows the catheter 2700 correctly inflated in the bladder 2020and then, if needed, pulled proximally so that the inflated balloon 2810rests against and substantially seals off the urethra 2030 from theinterior of the bladder 2020.

The stretch-valve of the exemplary embodiment of FIGS. 27 to 29 hasthree different aspects. The first is a hollow, stretch-valve tube 2820that is disposed in the inflation lumen 2722 to not hinder inflation ofthe balloon 2810 with the fluid 2200. While the diameter of thestretch-valve tube 2820 can be any size that accommodates unhinderedfluid flow through the inflation lumen 2722, one exemplary innerdiameter of the stretch-valve tube 2820 is substantially equal to thediameter of the inflation lumen 2722 and the outer diameter of thestretch-valve tube 2820 is just slightly larger than the diameter of theinflation lumen 2722 (e.g., the wall thickness of the tube can bebetween 0.05 mm and 0.2 mm). The proximal end of the stretch-valve tube2820 in this exemplary embodiment is proximal of a proximal end of theballoon inner wall 2730. The distal end of the stretch-valve tube 2820is somewhere near the proximal end of the balloon inner wall 2730; thedistal end can be proximal, at, or distal to the proximal end of theballoon inner wall 2730 and selection of this position is dependent uponthe amount of stretch S required to actuate the stretch-valve of theinventive catheter 2700 as described below. In the exemplary embodimentof FIG. 28, the distal end of the stretch-valve tube 2820 is shownbetween the inflation port 2724 and the proximal end of the ballooninner wall 2730. Two ports are formed, one proximal of the balloon 2810and one between the inflation port 2724 and the proximal end of theballoon inner wall 2730. A proximal port 2750 is formed through theouter wall 2740 through the inflation lumen wall 2720 to overlap atleast a portion of the proximal end of the stretch-valve tube 2820. Inthis manner, a portion of the outer surface of the proximal end of thestretch-valve tube 2820 at the proximal port 2750 is exposed to theenvironment but there is no fluid communication between the inflationlumen 2722 and the proximal port 2750. A distal port (white) 2760 isformed through both inflation lumen wall 2720 and the inner wall 2710distal of the proximal connection of the balloon inner wall 2730 tooverlap a least a portion of the distal end of the stretch-valve tube2820. In this manner, opposing portions of the outer surface of thedistal end of the stretch-valve tube 2820 at the distal port 2760 areexposed, one exposed to the interior of the balloon 2810 and one exposedto the drainage lumen 2712 but there is no fluid communication betweeneither the inflation lumen 2722 or the drainage lumen 2712 and thedistal port 2760. To secure the stretch-valve tube 2820 in the catheter2700, the proximal port 2750 is filled with a material that fixes theproximal end of the stretch-valve tube 2820 to at least one of the outerwall 2740 and the inflation lumen wall 2720. In one exemplaryembodiment, an adhesive bonds the proximal end of the stretch-valve tube2820 to both the outer wall 2740 and the inflation lumen wall 2720. Inthe exemplary embodiment, the adhesive can be the same material as anyor all of the walls 2710, 2720, 2730, 2740 or it can be a differentmaterial. If the outer wall 2740 is formed by a dipping of the interiorparts into a liquid bath of the same material as, for example, a duallumen extrusion including the inner wall 2710 and the inflation lumenwall 2720, then, when set, the outer wall 2740 will be integral to boththe inner wall 2710 and the inflation lumen wall 2720 and will befixedly connected to the stretch-valve tube 2820 through the proximalport 2750.

In such a configuration, therefore, any proximal movement of thecatheter 2700 at or proximal to the proximal port 2750 will also movethe stretch-valve tube 2820 proximally; in other words, the distal endof the stretch-valve tube 2820 can slide S within the inflation lumen2722 in a proximal direction. FIG. 29 illustrates how the slide-valve ofthe invention operates when the proximal end of the catheter 2700 ispulled to a force that is no greater than just before injury would occurto the urethrovesical junction or the urethra if the catheter 2700 wasstill inflated when the force was imparted. In an exemplary embodimentof the stretch valve of FIGS. 27 to 29, a pulling force in a range of 1to 15 pounds will cause the stretch-valve tube 2820 to slide proximallyS to place the distal end of the stretch-valve tube 2820 just proximalof the distal port 2760, i.e., the deflation point of the stretch-valveshown in FIG. 29. In another exemplary embodiment, the range of forcerequired to meet the deflation point is between 1 and 5 pounds, inparticular, between 1.5 and 2 pounds.

As can be seen in FIG. 29, when the deflation point of the stretch-valveis reached, the interior of the balloon 2810 becomes fluidicallyconnected to both the upper and lower portions of the distal port 2760in a direct and straight line. Because the distal port 2760 is open tothe drainage lumen 2712 (which is open the interior of the bladder 2020and to the non-illustrated, proximal drain bag) and due to the fact thatthe bladder is relatively unpressurized as compared to the balloon 2810,all internal pressure is released from the balloon 2810 to eject theinflating fluid 2200 into the drainage lumen 2712 (depicted by dashedarrows), thereby causing the balloon 2810 to deflate rapidly (depictedby solid opposing arrows). Unlike the embodiments above, the distance Xbetween the deflation port (the upper part of distal port 2760) and thelower part of distal port 2760 is zero—therefore, the rate at which theballoon 2510 deflates cannot be made any faster (other than expandingthe area of the distal port 2760). It is further noted that theinflation port 2724 also becomes fluidically connected to the drainlumen 2712 and, therefore, drainage of the fluid 2200 occurs through theinflation port 2724 as well. The cross-sectional area of the inflationlumen 2722, therefore, only slightly impacts the rate of balloondeflation, if at all. One way to speed up deflation can be to shape thedistal port 2760 in the form of a funnel outwardly expanding in adirection from the outer circumference of the catheter 2700 inwardstowards the drainage lumen 2712. Another way to speed up deflation canbe to have two or more inflation lumens 2722 about the circumference ofthe inner lumen wall 2710 and to have corresponding sets of astretch-valve tube 2820, a proximal port 2750, and a distal port 2760for each inflation lumen 2722.

FIG. 30 reproduces FIG. 27 to assist in explaining FIGS. 31 and 32 onthe same page. FIGS. 31 and 32 show, respectively, the closed and openedpositions of the stretch-valve tube 2820 in FIGS. 28 and 29. Thesefigures are viewed in an orientation turned ninety degreescounterclockwise with regard to a central, longitudinal axis of thecatheter 2700 viewed along the axis towards the distal end from theproximal end so that the view looks down upon the distal port 2760. Ascan be seen, without pulling on the proximal end of the catheter 2700(FIG. 31), the stretch-valve tube 2820 blocks the distal port 2760. Witha proximal force on the proximal end of the catheter 2700, as shown inFIG. 32, the stretch-valve tube 2820 slides and no longer blocks thedistal port 2760.

FIGS. 33 to 36 show alternative exemplary embodiments for theautomatically deflating, stretch-valve, safety balloon catheteraccording to the invention. Where various parts of the embodiments arenot described with regard to these figures (e.g., the balloon interiorwall), the above-mentioned parts are incorporated by reference hereininto these embodiments and are not repeated for reasons of brevity.

FIG. 33 illustrates the balloon portion of the inventive catheter 3300with the balloon 3302 in a partially inflated state. An annular innerlumen wall 3310 defines therein a drainage lumen 3312. At one or morecircumferential longitudinal extents about the inner lumen wall 3310, aninflation lumen wall 3320 defines an inflation lumen 3322 and a ballooninflation port 3324 fluidically connected to the inflation lumen 3322;in the inventive catheter, there can be more than one inflation lumen3322 and corresponding inflation port 3324 even though only one is shownherein. Accordingly, the views of FIGS. 33 to 36 show a cross-sectionthrough the single inflation lumen and single inflation port. No lumenplug closes the inflation lumen 3322 distal of the inflation port 3324as set forth above in alternative embodiments. In this exemplaryembodiment, a stretch-valve mechanism 3330 serves to plug the inflationlumen 3322 distal of the inflation port 3324 as described in furtherdetail below. An outer wall 3340 covers all of the interior walls 3310and 3320 in a fluid-tight manner and forms the exterior of the balloon3342 but does not cover the distal end of the inflation lumen 3322. Theouter wall 3340 is formed in any way described herein and is notdiscussed in further detail here.

The stretch-valve mechanism 3330 is disposed in the inflation lumen 3322to not hinder inflation of the balloon 3302 with inflating fluid. Aproximal, hollow anchor portion 3332 is disposed in the inflation lumen3320 proximal of the inflation port 3324. While the diameter of thehollow anchor portion 3332 can be any size that accommodates unhinderedfluid flow through the inflation lumen 3322, one exemplary innerdiameter of the hollow anchor portion 3332 is substantially equal to thediameter of the inflation lumen 3322 and the outer diameter of thehollow anchor portion 3332 is just slightly larger than the diameter ofthe inflation lumen 3322 (e.g., the wall thickness of the tube can bebetween 0.05 mm and 0.2 mm). The longitudinal length of the hollowanchor portion 3332 is as long as desired to be longitudinally fixedlysecured within the inflation lumen 3322 when installed in place. Thetube, from its shape alone, can provide the securing connection but,also, an adhesive can be used in any manner, one of which includescreating a proximal port as shown in the above embodiments and utilizingthe dipped exterior to form the fixed connection. The distal end of thehollow anchor portion 3332 in this exemplary embodiment is proximal of aproximal end of the balloon 3302. The distal end of the hollow anchorportion 3332 can be nearer to the inflation port 3324, but not at ordistal of the inflation port 3324; both ends of the hollow anchorportion 3332 can be proximal, at, or distal to the proximal end of theballoon 3302 and selection of this position is dependent upon the amountof stretch that is desired to actuate the stretch-valve of the inventivecatheter 3300 as described below. In the exemplary embodiment of FIG.33, the stretch-valve mechanism 3330 also includes an intermediatestopper wire 3334 connected at its proximal end to the hollow anchorportion 3332 and a stopper 3336 connected to the distal end of thestopper wire 3334. The stopper 3336 is sized to be slidably disposed inthe inflation lumen 3322 while, at the same time, to provide afluid-tight seal so that liquid cannot pass from one side of the stopper3336 to the other side within the inflation lumen 3322. The stopper 3336is located distal of the inflation port 3324. The stopper wire 3334,therefore, spans the inflation port 3324. Because the stopper 3336 musttraverse the inflation port 3324, it must be just distal of theinflation port 3324 but the hollow anchor portion can be locatedanywhere proximal of the inflation port 3324. While the length of thestopper wire 3334 needs to be sufficient to span the inflation port3324, it can be as long as desired, which will depend on where thehollow anchor portion 3332 resides as well as the amount of stretchdesired. As the catheter 3300 stretches more at its proximal end andless at its distal end when pulled from the proximal end, the hollowanchor portion 3322 can be further proximal in the inflation lumen 3322than shown, and can even be very close to or at the proximal end of theinflation lumen 3322.

In such a configuration, therefore, any proximal movement of thecatheter 3300 at or proximal to the inflation port 3324 will also movethe stretch-valve mechanism 3330 proximally; in other words, the stopper3336 slides proximally within the inflation lumen 3322 from distal ofthe inflation port 3324 to a proximal side of the inflation port 3324.When the proximal end of the catheter 3300 is pulled to move the stopper3336 across the inflation port 3324 with a force that is no greater thanjust before injury would occur to the urethrovesical junction or theurethra if the catheter 3300 was still inflated when the force wasimparted, fluid in the balloon 3342 can exit distally out the inflationlumen 3322. In an exemplary embodiment of the stretch valve of FIG. 33,a pulling force in a range of 1 to 15 pounds will cause thestretch-valve mechanism 3330 to slide proximally to place the stopper3336 just proximal of the inflation port 3324, i.e., the deflation pointof the stretch-valve shown in FIG. 33. In another exemplary embodiment,the range of force required to meet the deflation point is between 1 and5 pounds, in particular, between 1.5 and 2 pounds. When the stopper 3336traverses the inflation port 3324, the balloon 3342 automaticallydeflates and the inflating fluid exits into the bladder out the distalend of the inflation lumen 3332, which is open at the distal end of thecatheter 3300.

FIG. 34 illustrates the balloon portion of the inventive catheter 3400with the balloon 3402 in a partially inflated state. An annular innerlumen wall 3410 defines therein a drainage lumen 3412. At one or morecircumferential longitudinal extents about the inner lumen wall 3410, aninflation lumen wall 3420 defines an inflation lumen 3422 and a ballooninflation port 3424 fluidically connected to the inflation lumen 3422;in the inventive catheter, there can be more than one inflation lumen3422 and corresponding inflation port 3424 even though only one is shownherein. No lumen plug closes the inflation lumen 3422 distal of theinflation port 3424 as set forth above in alternative embodiments. Inthis exemplary embodiment, a stretch-valve mechanism 3430 serves to plugthe inflation lumen 3422 distal of the inflation port 3424 as describedin further detail below. An outer wall 3440 covers all of the interiorwalls 3410 and 3420 in a fluid-tight manner and forms the exterior ofthe balloon 3442 but does not cover the distal end of the inflationlumen 3422. The outer wall 3440 is formed in any way described hereinand is not discussed in further detail here.

The stretch-valve mechanism 3430 is disposed in the inflation lumen 3422and does not hinder inflation of the balloon 3402 with inflating fluid.A proximal, hollow anchor portion 3432 is disposed in the inflationlumen 3420 proximal of the inflation port 3424. While the diameter ofthe hollow anchor portion 3432 can be any size that accommodatesunhindered fluid flow through the inflation lumen 3422, one exemplaryinner diameter of the hollow anchor portion 3432 is substantially equalto the diameter of the inflation lumen 3422 and the outer diameter ofthe hollow anchor portion 3432 is just slightly larger than the diameterof the inflation lumen 3422 (e.g., the wall thickness of the tube can bebetween 0.05 mm and 0.2 mm). The longitudinal length of the hollowanchor portion 3432 is as long as desired to be longitudinally fixedlysecured within the inflation lumen 3422 when installed in place. Thetube, from its shape alone, can provide the securing connection but,also, an adhesive can be used in any manner, one of which includescreating a proximal port as shown in the above embodiments and utilizingthe dipped exterior to form the fixed connection. The distal end of thehollow anchor portion 3432 in this exemplary embodiment is at a proximalside of the balloon 3402. The distal end of the hollow anchor portion3432 can be nearer to the inflation port 3424, but not at or distal ofthe inflation port 3424; both ends of the hollow anchor portion 3432 canbe proximal, at, or distal to the proximal end of the balloon 3402 andselection of this position is dependent upon the amount of stretch thatis desired to actuate the stretch-valve of the inventive catheter 3400as described below. In the exemplary embodiment of FIG. 34, thestretch-valve mechanism 3430 also includes an intermediate hollowstopper tube 3434 connected at its proximal end to the hollow anchorportion 3432 and a stopper 3436 connected to the distal end of thestopper tube 3434. The stopper tube 3434 is only a circumferentialportion of the hollow anchor portion 3432 and is located opposite theinflation port 3424 so that it does not obstruct fluid flow through theinflation port 3424. The stopper, in contrast, is a solid cylinderhaving the same outer diameter as the hollow anchor portion 3432. Theentire mechanism 3430 is sized to be slidably disposed in the inflationlumen 3422 while, at the same time, to provide a fluid-tight seal at thestopper 3436 so that liquid cannot pass from one side of the stopper3436 to the other side within the inflation lumen 3422. The stopper 3436is located distal of the inflation port 3424. The stopper tube 3434,therefore, spans the inflation port 3424. Because the stopper 3436 musttraverse the inflation port 3424, it must be just distal of theinflation port 3424 but the hollow anchor portion 3432 can be locatedanywhere proximal of the inflation port 3424. While the length of thestopper tube 3434 needs to be sufficient to span the inflation port3424, it can be as long as desired, which will depend on where thehollow anchor portion 3432 resides. As the catheter 3400 stretches moreat its proximal end and less at its distal end when pulled from theproximal end, the hollow anchor portion 3422 can be further proximal inthe inflation lumen 3422 than shown, and can even be very close to or atthe proximal end of the inflation lumen 3422.

In such a configuration, therefore, any proximal movement of thecatheter 3400 at or proximal to the inflation port 3424 will also movethe stretch-valve mechanism 3430 proximally; in other words, the stopper3436 slides proximally within the inflation lumen 3422 from distal ofthe inflation port 3424 to a proximal side of the inflation port 3424.When the proximal end of the catheter 3400 is pulled to move the stopper3436 across the inflation port 3424 with a force that is no greater thanjust before injury would occur to the urethrovesical junction or theurethra if the catheter 3400 was still inflated when the force wasimparted, fluid in the balloon 3442 can exit distally out the inflationlumen 3422. In an exemplary embodiment of the stretch valve of FIG. 34,a pulling force in a range of 1 to 15 pounds will cause thestretch-valve mechanism 3430 to slide proximally to place the stopper3436 just proximal of the inflation port 3424, i.e., the deflation pointof the stretch-valve shown in FIG. 34. In another exemplary embodiment,the range of force required to meet the deflation point is between 1 and5 pounds, in particular, between 1.5 and 2 pounds. When the stopper 3436traverses the inflation port 3424, the balloon 3442 automaticallydeflates and the inflating fluid exits into the bladder out the distalend of the inflation lumen 3432, which is open at the distal end of thecatheter 3400.

FIG. 35 illustrates the balloon portion of the inventive catheter 3500with the balloon 3502 in a partially inflated state. An annular innerlumen wall 3510 defines therein a drainage lumen 3512. At one or morecircumferential longitudinal extents about the inner lumen wall 3510, aninflation lumen wall 3520 defines an inflation lumen 3522 and a ballooninflation port 3524 fluidically connected to the inflation lumen 3522;in the inventive catheter, there can be more than one inflation lumen3522 and corresponding inflation port 3524 even though only one is shownherein. No lumen plug closes the inflation lumen 3522 distal of theinflation port 3524 as set forth above in alternative embodiments. Inthis exemplary embodiment, a stretch-valve mechanism 3530 serves to plugthe inflation lumen 3522 distal of the inflation port 3524 as describedin further detail below. An outer wall 3540 covers all of the interiorwalls 3510 and 3520 in a fluid-tight manner and forms the exterior ofthe balloon 3542 but does not cover the distal end of the inflationlumen 3522. The outer wall 3540 is formed in any way described hereinand is not discussed in further detail here.

The stretch-valve mechanism 3530 is disposed in the inflation lumen 3522to not hinder inflation of the balloon 3502 with inflating fluid. Aproximal, hollow anchor portion 3532 is disposed in the inflation lumen3520 proximal of the inflation port 3524. While the diameter of thehollow anchor portion 3532 can be any size that accommodates unhinderedfluid flow through the inflation lumen 3522, one exemplary innerdiameter of the hollow anchor portion 3532 is substantially equal to thediameter of the inflation lumen 3522 and the outer diameter of thehollow anchor portion 3532 is just slightly larger than the diameter ofthe inflation lumen 3522 (e.g., the wall thickness of the tube can bebetween 0.05 mm and 0.2 mm). The longitudinal length of the hollowanchor portion 3532 is as long as desired to be longitudinally fixedlysecured within the inflation lumen 3522 when installed in place. Thetube, from its shape alone, can provide the securing connection but,also, an adhesive can be used in any manner, one of which includescreating a proximal port as shown in the above embodiments and utilizingthe dipped exterior to form the fixed connection. The distal end of thehollow anchor portion 3532 in this exemplary embodiment is at a proximalside of the balloon 3502. The distal end of the stretch-valve mechanism3530 can be nearer to the inflation port 3524, but not at or distal ofthe inflation port 3524; both ends of the hollow anchor portion 3532 canbe proximal, at, or distal to the proximal end of the balloon 3502 andselection of this position is dependent upon the amount of stretch thatis desired to actuate the stretch-valve of the inventive catheter 3500as described below. In the exemplary embodiment of FIG. 35, thestretch-valve mechanism 3530 also includes an intermediate bias device3534, such as a spring, connected at its proximal end to the hollowanchor portion 3532 and a stopper 3536 connected to the distal end ofthe bias device 3534. The bias device 3534 is located at the inflationport 3524 but not to obstruct fluid flow through the inflation port3524. The stopper 3536, in contrast, is a solid cylinder having the sameouter diameter as the hollow anchor portion 3532. The entire mechanism3530 is sized to be slidably disposed in the inflation lumen 3522 while,at the same time, to provide a fluid-tight seal at the stopper 3536 sothat liquid cannot pass from one side of the stopper 3536 to the otherside within the inflation lumen 3522. The stopper 3536 is located distalof the inflation port 3524. To prevent distal movement of the stopper3536, a restrictor 3538 is provided distal of the stopper 3536. The biasdevice 3534, therefore, spans the inflation port 3524. Because thestopper 3536 must traverse the inflation port 3524, it must be justdistal of the inflation port 3524 but the hollow anchor portion 3532 canbe located anywhere proximal of the inflation port 3524. While thelength of the bias device 3534 needs to be sufficient to span theinflation port 3524, it can be as long as desired, which will depend onwhere the hollow anchor portion 3532 resides. As the catheter 3500stretches more at its proximal end and less at its distal end whenpulled from the proximal end, the hollow anchor portion 3522 can befurther proximal in the inflation lumen 3522 than shown, and can even bevery close to or at the proximal end of the inflation lumen 3522.

In such a configuration, therefore, any proximal movement of thecatheter 3500 at or proximal to the inflation port 3524 will also movethe stretch-valve mechanism 3530 proximally; in other words, the stopper3536 slides proximally within the inflation lumen 3522 from distal ofthe inflation port 3524 to a proximal side of the inflation port 3524.When the proximal end of the catheter 3500 is pulled to move the stopper3536 across the inflation port 3524 with a force that is no greater thanjust before injury would occur to the urethrovesical junction or theurethra if the catheter 3500 was still inflated when the force wasimparted, fluid in the balloon 3542 can exit distally out the inflationlumen 3522. In an exemplary embodiment of the stretch valve of FIG. 35,a pulling force in a range of 1 to 15 pounds will cause thestretch-valve mechanism 3530 to slide proximally to place the stopper3536 just proximal of the inflation port 3524, i.e., the deflation pointof the stretch-valve shown in FIG. 35. In another exemplary embodiment,the range of force required to meet the deflation point is between 1 and5 pounds, in particular, between 1.5 and 2 pounds. When the stopper 3536traverses the inflation port 3524, the balloon 3542 automaticallydeflates and the inflating fluid exits into the bladder out the distalend of the inflation lumen 3532, which is open at the distal end of thecatheter 3500.

FIG. 36 illustrates the balloon portion of the inventive catheter 3600with the balloon 3602 in a partially inflated state. An annular innerlumen wall 3610 defines therein a drainage lumen 3612. At one or morecircumferential longitudinal extents about the inner lumen wall 3610, aninflation lumen wall 3620 defines an inflation lumen 3622 and a ballooninflation port 3624 fluidically connected to the inflation lumen 3622;in the inventive catheter, there can be more than one inflation lumen3622 and corresponding inflation port 3624 even though only one is shownherein. No lumen plug closes the inflation lumen 3622 distal of theinflation port 3624 as set forth above in alternative embodiments. Inthis exemplary embodiment, a stretch-valve mechanism 3630 serves to plugthe inflation lumen 3622 distal of the inflation port 3624 as describedin further detail below. An outer wall 3640 covers all of the interiorwalls 3610 and 3620 in a fluid-tight manner and forms the exterior ofthe balloon 3642 but does not cover the distal end of the inflationlumen 3622. The outer wall 3640 is formed in any way described hereinand is not discussed in further detail here.

The stretch-valve mechanism 3630 is disposed in the inflation lumen 3622to not hinder inflation of the balloon 3602 with inflating fluid. Anon-illustrated proximal anchor is disposed in the inflation lumen 3620proximal of the inflation port 3624. The proximal anchor can be any sizeor shape that accommodates unhindered fluid flow through the inflationlumen 3622, one exemplary inner diameter of the hollow anchor portion3632 is a tube substantially equal to the diameter of the inflationlumen 3622 with an outer diameter just slightly larger than the diameterof the inflation lumen 3622 (e.g., the thickness of the tube can bebetween 0.07 mm and 0.7 mm). The longitudinal length of this hollowanchor can be as long as desired to be longitudinally fixedly securedwithin the inflation lumen 3622 when installed in place. The anchor inthis exemplary embodiment is at or near the non-illustrated proximal endof the inflation lumen 3622. The distal end of the stretch-valvemechanism 3630 can be nearer to the inflation port 3624, but not at ordistal of the inflation port 3624; selection of the anchor's position isdependent upon the amount of stretch that is desired to actuate thestretch-valve of the inventive catheter 3600 as described below. In theexemplary embodiment of FIG. 36, the stretch-valve mechanism 3630 alsoincludes an intermediate cord 3634, either inelastic or elastic,connected at its proximal end to the anchor. A stopper 3636 is connectedto the distal end of the cord 3634. The cord 3634 is located at theinflation port 3624 but not to obstruct fluid flow through the inflationport 3624. The stopper 3636, in contrast, is a solid cylinder having thea diameter that allows it to slidably move within the inflation lumen3622 when the cord 3634 pulls it but, at the same time, to provide afluid-tight seal so that liquid cannot pass from one side of the stopper3636 to the other side within the inflation lumen 3622. The stopper 3636is located distal of the inflation port 3624. To prevent distal movementof the stopper 3636, a restrictor 3638 is provided distal of the stopper3636. The cord 3634, therefore, spans the inflation port 3624. Becausethe stopper 3636 must traverse the inflation port 3624, it must be justdistal of the inflation port 3624 but the anchor can be located anywhereproximal of the inflation port 3624. While the length of the cord 3634needs to be sufficient to span the inflation port 3624, it can be aslong as desired, which will depend on where the anchor resides. As thecatheter 3600 stretches more at its proximal end and less at its distalend when pulled from the proximal end, the anchor can be furtherproximal in the inflation lumen 3622 than shown, and can even be veryclose to or at the proximal end of the inflation lumen 3622. It can evenbe attached to the luer connector half that prevents fluid from flowingout the proximal end of the inflation lumen 3622.

In such a configuration, therefore, any proximal movement of thecatheter 3600 at the proximal end where the anchor resides will alsomove the stretch-valve mechanism 3630 proximally; in other words, thestopper 3636 slides proximally within the inflation lumen 3622 fromdistal of the inflation port 3624 to a proximal side of the inflationport 3624. When the proximal end of the catheter 3600 is pulled to movethe stopper 3636 across the inflation port 3624 with a force that is nogreater than just before injury would occur to the urethrovesicaljunction or the urethra if the catheter 3600 was still inflated when theforce was imparted, fluid in the balloon 3642 can exit distally out theinflation lumen 3622. In an exemplary embodiment of the stretch valve ofFIG. 36, a pulling force in a range of 1 to 15 pounds will cause thestretch-valve mechanism 3630 to slide proximally to place the stopper3636 just proximal of the inflation port 3624, i.e., the deflation pointof the stretch-valve shown in FIG. 36. In another exemplary embodiment,the range of force required to meet the deflation point is between 1 and5 pounds, in particular, between 1.5 and 2 pounds. When the stopper 3636traverses the inflation port 3624, the balloon 3642 automaticallydeflates and the inflating fluid exits into the bladder out the distalend of the inflation lumen 3632, which is open at the distal end of thecatheter 3600.

An alternative exemplary embodiment combines the embodiments of FIGS. 30and 36 to tether the tube 2820 at the proximal end of the catheter.

FIG. 37 illustrates the balloon portion of the inventive catheter 3700with the balloon 3742 in a partially inflated state. An annular innerlumen wall 3710 defines therein a drainage lumen 3712. At one or morecircumferential longitudinal extents about the inner lumen wall 3710, aninflation lumen wall 3720 defines an inflation lumen 3722 and a ballooninflation port 3724 fluidically connected to the inflation lumen 3722;in the inventive catheter, there can be more than one inflation lumen3722 and corresponding inflation port 3724 even though only one is shownherein. A lumen plug 3736 fluidically closes the inflation lumen 3722distal of the inflation port 3724 so that all inflation fluid 3702 isdirected into the balloon 3742. The lumen plug 3736 can plug any pointor extent from the inflation port 3724 distally. An outer wall 3740covers all of the interior walls 3710 and 3720 in a fluid-tight mannerand forms the exterior of the balloon 3742 but does not cover the distalend of the drainage lumen 3712. The outer wall 3740 is formed in any waydescribed herein and is not discussed in further detail here.

In this exemplary embodiment, a hollow, stretch-valve tube 3730 isdisposed in the drainage lumen 3712 to not hinder drainage of the fluidto be drained (e.g., urine). While the diameter of the stretch-valvetube 3730 can be any size that accommodates unhindered fluid flowthrough the drainage lumen 3712, one exemplary inner diameter of thestretch-valve tube 3730 is substantially equal to the diameter of thedrainage lumen 3712 and the outer diameter of the stretch-valve tube3730 is just slightly larger than the diameter of the drainage lumen3712 (e.g., the wall thickness of the tube can be between 0.07 mm and0.7 mm). The proximal end of the stretch-valve tube 3830 in thisexemplary embodiment is proximal of a proximal end of a deflation port3760. The distal end of the stretch-valve tube 3730 is not distal of thedistal end of the balloon 3742 so that the balloon 3742 can be deflated;the distal end can be anywhere between the two ends of the balloon 3742but is shown in an intermediate position in FIG. 37. The distal end ofthe stretch-valve tube 3730 is at a distance distal of the deflationport 3760 and selection of this distance S is dependent upon the amountof stretch required to actuate the stretch-valve of the inventivecatheter 3700 as described below. In the exemplary embodiment of FIG.37, the longitudinal length of the deflation port 3760 is shown as lessthan one half of the longitudinal length of the stretch-valve tube 3730.The drainage port 3760 is formed through the inner lumen wall 3710 andthe stretch-valve tube 3730 is positioned to overlap at least thedrainage port 3760. In this manner, a portion of the outer surface ofthe proximal end of the stretch-valve tube 3730 closes off the drainageport 3760 to prevent fluid communication between the balloon 3742 andthe drainage lumen 3712 through the drainage port 3760.

To secure the stretch-valve tube 3730 in the catheter 3700, a proximalanchor 3732 is disposed in the drainage lumen 3710 away from thedeflation port 3760, here proximally. The proximal anchor 3732 can beany size or shape that accommodates unhindered fluid flow through thedrainage lumen 3712, one exemplary inner diameter of the hollow anchor3732 being a tube or ring substantially equal to the diameter of thedrainage lumen 3712 with an outer diameter just slightly larger than thediameter of the drainage lumen 3712 (e.g., the thickness of the tube canbe between 0.07 mm and 0.7 mm). The longitudinal length of this hollowanchor 3732 can be as long as desired but just enough to longitudinallyfixedly secure the stretch-valve tube 3730 within the drainage lumen3712 when installed in place. The anchor 3732 in this exemplaryembodiment is at the proximal end of the balloon 3742 but can be furtherinside the balloon 3742 (distal) or entirely proximal of the balloon3742. In an exemplary embodiment, the anchor 3732 has a stepped distalorifice that permits the proximal end of the stretch-valve tube 3730 tobe, for example, press-fit therein for permanent connection. In anotherexemplary embodiment, the anchor 3732 is an adhesive or glue that fixesthe proximal end of the stretch-valve tube 3730 longitudinally in placewithin the drainage lumen 3712. The adhesive can be the same material asany or all of the walls 3710, 3720, 3740 or it can be a differentmaterial. In an exemplary non-illustrated embodiment where a fixationport or set of fixation ports are formed through the inner wall 3710proximal of the proximal-most end of the balloon 3742 and about theproximal end of the stretch-valve tube 3730, if the outer wall 3740 isformed by a dipping of the interior parts into a liquid bath of the samematerial as, for example, a dual lumen extrusion including the innerwall 3710 and the inflation lumen wall 3720, then, when set, the outerwall 3740 will be integral to both the inner wall 3710 and the inflationlumen wall 3720 and will be fixedly connected to the stretch-valve tube3730 through the fixation port(s).

In such a configuration, therefore, any proximal movement of thecatheter 3700 at or proximal to the drainage port 3760 will also movethe stretch-valve tube 3730 proximally; in other words, the distal endof the stretch-valve tube 3730 can slide within the drainage lumen 3712in a proximal direction. When the proximal end of the catheter 3700 ispulled to a force that is no greater than just before injury would occurto the urethrovesical junction or the urethra if the catheter 3700 wasstill inflated when the force was imparted, the force will cause thestretch-valve tube 3730 to slide proximally to place the distal end ofthe stretch-valve tube 3730 just proximal of the drainage port 3760,e.g., with a pulling force in a range of 1 to 15 pounds. In anotherexemplary embodiment, the range of force required to meet the deflationpoint is between 1 and 5 pounds, in particular, between 1.5 and 2pounds.

When the deflation point of the stretch-valve tube 3730 starts, theinterior of the balloon 3742 becomes fluidically connected directly intothe drainage lumen 3712 (which is open to the interior of the bladder2020 and to the non-illustrated, proximal drain bag) and, due to thefact that the bladder is relatively unpressurized as compared to theballoon 3742, all internal pressure is released from the balloon 3742 toeject the inflating fluid 3702 directly into the drainage lumen 3712,thereby causing the balloon 3742 to deflate rapidly. Because there is nointermediate structure between the balloon inflating fluid 3702 and thedrainage lumen 3712, the rate at which the balloon 3742 deflates isfast. One way to speed up deflation can be to shape the drainage port3760 in the form of a funnel outwardly expanding in a direction from theouter wall 3740 towards the interior of the catheter 3700. Another wayto speed up deflation can be to have two or more drainage ports 3760about the circumference of the inner lumen wall 3710 and/or to enlargethe cross-sectional area of the drainage port 3760.

FIG. 38 illustrates a balloon portion of the inventive catheter 3800with a balloon 3842 in a partially inflated state. An annular innerlumen wall 3810 defines therein a drainage lumen 3812. At one or morecircumferential longitudinal extents about the inner lumen wall 3810, aninflation lumen wall 3820 defines an inflation lumen 3822 and a ballooninflation port 3824 fluidically connected to the inflation lumen 3822;in the inventive catheter, there can be more than one inflation lumen3822 and corresponding inflation port 3824 even though only one is shownherein. A lumen plug 3836 fluidically closes the inflation lumen 3822distal of the inflation port 3824 so that all inflation fluid 3802 isdirected into the balloon 3842. The lumen plug 3736 can plug any pointor extent from the inflation port 3724 distally. An outer wall 3840covers all of the interior walls 3810 and 3820 in a fluid-tight mannerand forms the exterior of the balloon 3842 but does not cover the distalend of the drainage lumen 3812. The outer wall 3840 is formed in any waydescribed herein and is not discussed in further detail here.

In this exemplary embodiment, a hollow, stretch-valve tube 3830 isdisposed in the drainage lumen 3812 to not hinder drainage of the fluidto be drained (e.g., urine). While the diameter of the stretch-valvetube 3830 can be any size that accommodates unhindered fluid flowthrough the drainage lumen 3812, one exemplary inner diameter of thestretch-valve tube 3830 is substantially equal to the diameter of thedrainage lumen 3812 and the outer diameter of the stretch-valve tube3830 is just slightly larger than the diameter of the drainage lumen3812 (e.g., the wall thickness of the tube can be between 0.07 mm and0.7 mm). The proximal end of the stretch-valve tube 3830 in thisexemplary embodiment is proximal of a proximal end of a deflation port3860. The distal end of the stretch-valve tube 3830 is not distal of thedistal end of the balloon 3842 so that the balloon 3842 can be deflated;the distal end can be anywhere between the two ends of the balloon 3842but is shown in an intermediate position in FIG. 38. The distal end ofthe stretch-valve tube 3830 is at a distance S distal of the deflationport 3860 and selection of this distance S is dependent upon the amountof stretch required to actuate the stretch-valve of the inventivecatheter 3800 as described below. In the exemplary embodiment of FIG.38, the longitudinal length of the deflation port 3860 is shown as lessthan one half of the longitudinal length of the stretch-valve tube 3830.The drainage port 3860 is formed through the inner lumen wall 3810 andthe stretch-valve tube 3830 is positioned to overlap at least thedrainage port 3860. In this manner, a portion of the outer surface ofthe proximal end of the stretch-valve tube 3830 closes off the drainageport 3860 to prevent fluid communication between the balloon 3842 andthe drainage lumen 3812 through the drainage port 3860.

In this exemplary embodiment, in comparison to the embodiment of FIG.37, a second drainage port 3862 is provided in the inner lumen wall 3810aligned with the drainage port 3860, and both drainage ports 3860, 3862are aligned with the inflation port 3824. As such, when thestretch-valve tube 3830 moves proximally to uncover the drainage ports3860, 3862, inflation fluid 3802 from inside the balloon 3842 exits fromboth the inflation port 3824 and the drainage port 3860.

To secure the stretch-valve tube 3830 in the catheter 3800, a proximalanchor 3832 is disposed in the drainage lumen 3810 away from thedeflation ports 3860, 3862, here proximally. The proximal anchor 3832can be any size or shape that accommodates unhindered fluid flow throughthe drainage lumen 3812, one exemplary inner diameter of the hollowanchor 3832 being a tube or ring substantially equal to the diameter ofthe drainage lumen 3812 with an outer diameter just slightly larger thanthe diameter of the drainage lumen 3812 (e.g., the thickness of the tubecan be between 0.07 mm and 0.7 mm). The longitudinal length of thishollow anchor 3832 can be as long as desired but just enough tolongitudinally fixedly secure the stretch-valve tube 3830 within thedrainage lumen 3812 when installed in place. The anchor 3832 in thisexemplary embodiment is at the proximal end of the balloon 3842 but canbe further inside the balloon 3842 (distal) or entirely proximal of theballoon 3842. In an exemplary embodiment, the anchor 3832 has a steppeddistal orifice that permits the proximal end of the stretch-valve tube3830 to be, for example, press-fit therein for permanent connection. Inanother exemplary embodiment, the anchor 3832 is an adhesive or gluethat fixes the proximal end of the stretch-valve tube 3830longitudinally in place within the drainage lumen 3812. The adhesive canbe the same material as any or all of the walls 3810, 3820, 3840 or itcan be a different material. In an exemplary non-illustrated embodimentwhere a fixation port or set of fixation ports are formed through theinner wall 3810 proximal of the proximal-most end of the balloon 3842and about the proximal end of the stretch-valve tube 3830, if the outerwall 3840 is formed by a dipping of the interior parts into a liquidbath of the same material as, for example, a dual lumen extrusionincluding the inner wall 3810 and the inflation lumen wall 3820, then,when set, the outer wall 3840 will be integral to both the inner wall3810 and the inflation lumen wall 3820 and will be fixedly connected tothe stretch-valve tube 3820 through the fixation port(s).

In such a configuration, therefore, any proximal movement of thecatheter 3800 at or proximal to the drainage ports 3860, 3862 will alsomove the stretch-valve tube 3830 proximally; in other words, the distalend of the stretch-valve tube 3830 can slide within the drainage lumen3812 in a proximal direction. When the proximal end of the catheter 3800is pulled to a force that is no greater than just before injury wouldoccur to the urethrovesical junction or the urethra if the catheter 3800was still inflated when the force was imparted, the force will cause thestretch-valve tube 3830 to slide proximally to place the distal end ofthe stretch-valve tube 3830 just proximal of the drainage ports 3860,3862, e.g., with a pulling force in a range of 1 to 15 pounds. Inanother exemplary embodiment, the range of force required to meet thedeflation point is between 1 and 5 pounds, in particular, between 1.5and 2 pounds.

When the deflation point of the stretch-valve tube 3830 starts, theinterior of the balloon 3842 becomes fluidically connected directly intothe drainage lumen 3812 (which is open to the interior of the bladder2020 and to the non-illustrated, proximal drain bag) and, due to thefact that the bladder is relatively unpressurized as compared to theballoon 3842, all internal pressure is released from the balloon 3842 toeject the inflating fluid 3802 directly into the drainage lumen 3812,thereby causing the balloon 3842 to deflate rapidly. Because there is nointermediate structure between the balloon inflating fluid 3802 and thedrainage lumen 3812, the rate at which the balloon 3842 deflates isfast. One way to speed up deflation can be to shape the drainage ports3860, 3862 in the form of a funnel outwardly expanding in a directionfrom the outer wall 3840 towards the interior of the catheter 3800.Another way to speed up deflation can be to have two or more drainageports 3860 about the circumference of the inner lumen wall 3810 and/orto enlarge the cross-sectional area of the drainage ports 3860, 3862.

Reference is made to the flow chart of FIG. 39 to explain one exemplaryembodiment of a process for making a catheter according to theembodiment of FIGS. 21 to 23.

The catheter starts, in Step 3910 with a dual lumen extrusion of latex.This extrusion, therefore, defines the annular inner lumen wall 2110with the drainage lumen 2112 and, at one or more circumferentiallongitudinal extents about the inner lumen wall 2110, an inflation lumenwall 2120 with the inflation lumen 2122. The dual lumen, therefore,already includes both the drainage lumen 2112 and the inflation lumen2122. Both lumen 2112, 2122, however, are extruded without obstructionand without radial ports. Therefore, in order to have the inflation port2124, a radial hole needs to be created between the outside surface ofthe extrusion and the inflation lumen.

In step 3912, the balloon inflation port 2124 is made to fluidicallyconnect the environment of the extrusion to the inflation lumen 2122.

Sealing off of the distal end of the inflation lumen 2122 can beperformed in Step 3914 by inserting or creating a plug 2126 therein orthe sealing can occur simultaneously with the creation of the outer wall2140 below.

In step 3916, a balloon sleeve 2130 is placed about the inflation port2124 and is fixed to the exterior of the inflation lumen wall 2120 atboth ends to define a fluid-tight balloon interior 2200 therebetween. Assuch, inflation of the balloon 2210 can occur through the inflationlumen 2122. For example, the tube 2130 making up the inner balloon wallis slid over the distal end of the dual-lumen extrusion to cover theinflation port 2124 and is fluid-tightly sealed to the inner multi-lumenextrusion at both ends of the tube but not in the intermediate portion.This tube can be made of latex as well and, therefore, can be secured tothe latex multi-lumen extrusion in any known way to bond latex in afluid-tight manner.

In step 3918, the entire sub-assembly is covered with the outer wall2140. For example, the entire sub-assembly is dipped into latex in itsliquid form to create the outer wall 2140. In the alternative embodimentwhere a distal inflation lumen plug is not used, the latex can beallowed to enter at least a portion of the distal end of the inflationlumen 2122 but not so far as to block the inflation port 2124. When thelatex cures, the balloon 2210 is fluid tight and can only be fluidicallyconnected to the environment through the proximal-most opening of theinflation port, which is fluidically connected to the inflation lumen2122. In this process, the inner wall 2110, the inflation lumen wall2120, the plug 2126, the balloon wall 2130, and the outer wall 2140 areall made of the same latex material and, therefore, together, form avery securely water-tight balloon 2210.

The sub-process described in Steps 3910 to 3920 can be skipped ifdesired and, instead, completed by utilizing a standard Foley catheter,on which the following steps are performed.

The stretch valve is now created. A proximal port 2150 is formed throughthe outer wall 2140 and through the inflation lumen wall 2020 in step3920. A distal port 2160 is formed through the outer wall 2140 andthrough the inflation lumen wall 2020 in step 3922. Then, in step 3924,the stretch-valve tube 2220 is inserted through either one of theproximal or distal ports 2150, 2160 such that the proximal port 2150overlaps at least a portion of the proximal end of the stretch-valvetube 2220 and the distal port 2160 overlaps at least a portion of thedistal end of the stretch-valve tube 2220. In this manner, two portionsof the outer surface of the proximal end of the stretch-valve tube 2220at the proximal and distal ports 2150, 2160 are exposed to theenvironment but there is no fluid communication with the inflation lumen2122 and the proximal or distal ports 2150, 2160.

In Step 3926, the proximal port 2150 is used to secure the stretch-valvetube 2220 in the catheter 2100. In one exemplary embodiment, theproximal port 2150 is filled with a material that fixes the proximal endof the stretch-valve tube 2220 to at least one of the outer wall 2140and the inflation lumen wall 2020. In an exemplary embodiment, anadhesive bonds the proximal end of the stretch-valve tube 2220 to boththe outer wall 2140 and the inflation lumen wall 2120. In anotherexemplary embodiment, a portion of the present sub-assembly is dippedinto latex in its liquid form to plug the proximal port 2150 and fixedlysecure the stretch-valve tube 2220 to both the outer wall 2140 and theinflation lumen wall 2120. When the latex cures, the connection at theproximal port 2150 is fluid tight and no longer permits fluidicconnection to the environment therethrough. In this process, therefore,the filled proximal port 2150, the inflation lumen wall 2120, and theouter wall 2140 are all made of the same latex material and, therefore,together, form a very securely water-tight connection.

In such a configuration, therefore, any proximal movement of thecatheter 2100 at or proximal of the proximal port 2150 will also movethe stretch-valve tube 2220 proximally; in other words, the distal endof the stretch-valve tube 2220 can slide within the inflation lumen 2122in a proximal direction.

Reference is also made to the flow chart of FIG. 39 to explain oneexemplary embodiment of a process for making a catheter according to theembodiment of FIGS. 24 to 26.

The catheter starts, in Step 3910 with a dual lumen extrusion of latex.This extrusion, therefore, defines the annular inner lumen wall 2410with the drainage lumen 2412 and, at one or more circumferentiallongitudinal extents about the inner lumen wall 2410, an inflation lumenwall 2420 with the inflation lumen 2422. The dual lumen, therefore,already includes both the drainage lumen 2412 and the inflation lumen2422. Both lumens 2412, 2422, however, are extruded without obstructionand without radial ports. Therefore, in order to have the inflation port2424, a radial hole needs to be created between the outside surface ofthe extrusion and the inflation lumen.

In Step 3912, the balloon inflation port 2424 is made to fluidicallyconnect the environment of the extrusion to the inflation lumen 2422.

Sealing off of the distal end of the inflation lumen 2422 can beperformed in Step 3914 by inserting or creating a plug 2426 therein orthe sealing can occur simultaneously with the creation of the outer wall2440 below.

In Step 3916, a balloon sleeve 2430 is placed about the inflation port2424 and is fixed to the exterior of the inflation lumen wall 2420 atboth ends to define a fluid-tight balloon interior 2200 therebetween. Assuch, inflation of the balloon 2240 can occur through the inflationlumen 2422. For example, the tube 2430 making up the inner balloon wallis slid over the distal end of the dual-lumen extrusion to cover theinflation port 2424 and is fluid-tightly sealed to the inner multi-lumenextrusion at both ends of the tube but not in the intermediate portion.This tube can be made of latex as well and, therefore, can be secured tothe latex multi-lumen extrusion in any known way to bond latex in afluid-tight manner.

In Step 3918, the entire sub-assembly is covered with the outer wall2440. For example, the entire sub-assembly is dipped into latex in itsliquid form to create the outer wall 2440. In the alternative embodimentwhere a distal inflation lumen plug is not used, the latex can beallowed to enter at least a portion of the distal end of the inflationlumen 2422 but not so far as to block the inflation port 2424. When thelatex cures, the balloon 2240 is fluid tight and can only be fluidicallyconnected to the environment through the proximal-most opening of theinflation port, which is fluidically connected to the inflation lumen2422. In this process, the inner wall 2410, the inflation lumen wall2420, the plug 2426, the balloon wall 2430, and the outer wall 2440 areall made of the same latex material and, therefore, together, form avery securely water-tight balloon 2240.

The sub-process described in Steps 3910 to 3920 can be skipped ifdesired and, instead, completed by utilizing a standard Foley catheter,on which the following Steps are performed.

The stretch valve is now created. A proximal port 2450 is formed throughthe outer wall 2440 and through the inflation lumen wall 2020 in Step3920. A distal port 2460 is formed through the inner wall 2410 into theinflation lumen 2422 in Step 3922. Then, in Step 3924, the stretch-valvetube 2520 is inserted through either one of the proximal or distal ports2450, 2460 such that the proximal port 2450 overlaps at least a portionof the proximal end of the stretch-valve tube 2520 and the distal port2460 overlaps at least a portion of the distal end of the stretch-valvetube 2520. In this manner, one portion of the outer surface of theproximal end of the stretch-valve tube 2520 at the proximal port 2450 isexposed to the drain lumen 2412 and another portion of the outer surfaceof the distal end of the stretch-valve tube 2520 at the distal port 2460is exposed to the environment but there is no fluid communication withthe inflation lumen 2422 to either of the proximal or distal ports 2450,2460.

In Step 3926, the proximal port 2450 is used to secure the stretch-valvetube 2520 in the catheter 2400. In one exemplary embodiment, theproximal port 2450 is filled with a material that fixes the proximal endof the stretch-valve tube 2520 to at least one of the outer wall 2440and the inflation lumen wall 2020. In an exemplary embodiment, anadhesive bonds the proximal end of the stretch-valve tube 2520 to boththe outer wall 2440 and the inflation lumen wall 2420. In anotherexemplary embodiment, a portion of the present sub-assembly is dippedinto latex in its liquid form to plug the proximal port 2450 and fixedlysecure the stretch-valve tube 2520 to both the outer wall 2440 and theinflation lumen wall 2420. When the latex cures, the connection at theproximal port 2450 is fluid tight and no longer permits fluidicconnection to the environment therethrough. In this process, therefore,the filled proximal port 2450, the inflation lumen wall 2420, and theouter wall 2440 are all made of the same latex material and, therefore,together, form a very securely water-tight connection.

In such a configuration, therefore, any proximal movement of thecatheter 2400 at or proximal of the proximal port 2450 will also movethe stretch-valve tube 2520 proximally; in other words, the distal endof the stretch-valve tube 2520 can slide within the inflation lumen 2422in a proximal direction.

Reference is made to the flow chart of FIG. 40 to explain one exemplaryembodiment of a process for making a catheter according to theembodiment of FIGS. 27 to 29.

The catheter starts, in Step 4010 with a dual lumen extrusion of latex.This extrusion, therefore, defines the annular inner lumen wall 2710with the drainage lumen 2712 and, at one or more circumferentiallongitudinal extents about the inner lumen wall 2710, an inflation lumenwall 2720 with the inflation lumen 2722. The dual lumen, therefore,already includes both the drainage lumen 2712 and the inflation lumen2722. Both lumen 2712, 2722, however, are extruded without obstructionand without radial ports. Therefore, in order to have the inflation port2724, a radial hole needs to be created between the outside surface ofthe extrusion and the inflation lumen.

In Step 4012, the balloon inflation port 2724 is made to fluidicallyconnect the environment of the extrusion to the inflation lumen 2722.

Different from the other exemplary embodiments described, a distal port2760 is created in Step 4014 before, after, or at the same time as theballoon inflation port 2724. The distal port 2760 connects theenvironment to the interior of the drain lumen 2712. In an exemplaryembodiment, the distal port 2760 is proximal of the balloon inflationport 2724.

Sealing off of the distal end of the inflation lumen 2722 can beperformed in Step 4016 by inserting or creating a plug 2726 therein orthe sealing can occur simultaneously with the creation of the outer wall2740 below.

In Step 4018, a balloon sleeve 2730 is placed about the inflation port2724 and the distal port 2760 and is fixed to the exterior of theinflation lumen wall 2720 at both ends to define a fluid-tight ballooninterior 2200 therebetween. As such, inflation of the balloon 2810 canoccur through the inflation lumen 2722. For example, the tube 2730making up the inner balloon wall is slid over the distal end of thedual-lumen extrusion to cover the inflation port 2724 and isfluid-tightly sealed to the inner multi-lumen extrusion at both ends ofthe tube but not in the intermediate portion. This tube can be made oflatex as well and, therefore, can be secured to the latex multi-lumenextrusion in any known way to bond latex in a fluid-tight manner.

The stretch valve is now completed. A proximal port 2750 is formedthrough the inflation lumen wall 2020 in Step 4020. Then, in Step 4022,the stretch-valve tube 2820 is inserted through either one of theproximal or distal ports 2750, 2760 such that the proximal port 2750overlaps at least a portion of the proximal end of the stretch-valvetube 2820 and the distal port 2760 overlaps at least a portion of thedistal end of the stretch-valve tube 2820. In this manner, two portionsof the outer surface of the proximal end of the stretch-valve tube 2820at the proximal and distal ports 2750, 2760 are exposed to theenvironment but there is no fluid communication with the inflation lumen2722 and the proximal or distal ports 2750, 2760. Alternatively, Steps4022 can occur before 4018 to insert the stretch-valve tube 2820 beforethe balloon sleeve 2730 is placed and fixed. In such a case, thecreation of the proximal port 2750 can occur before, after, or at thesame time as creating the distal port 2760 and the balloon inflationport 2724, in which embodiment, all three ports 2724, 2750, 2760 can becreated at the same time.

In Step 4024, the entire sub-assembly is covered with the outer wall2740. For example, the entire sub-assembly is dipped into latex in itsliquid form to create the outer wall 2740. In the alternative embodimentwhere a distal inflation lumen plug is not used, the latex can beallowed to enter at least a portion of the distal end of the inflationlumen 2722 but not so far as to block the inflation port 2724. When thelatex cures, the balloon 2810 is fluid tight and can only be fluidicallyconnected to the environment through the proximal-most opening of theinflation port, which is fluidically connected to the inflation lumen2722. In this process, the inner wall 2710, the inflation lumen wall2720, the plug 2726, the balloon wall 2730, and the outer wall 2740 areall made of the same latex material and, therefore, together, form avery securely water-tight balloon 2810.

In previous embodiments, the proximal port 2750 pierced the outer wall2740. In this exemplary embodiment, however, there is no need to do so.Here, the proximal port 2750 can be filled with material of the outerwall 2740 itself to fix the proximal end of the stretch-valve tube 2820to at least one of the outer wall 2740 and the inflation lumen wall2020. When the latex cures, the connection at the proximal port 2750 isfluid tight and no longer permits fluidic connection to the environmenttherethrough. In this process, therefore, the filled proximal port 2750,the inflation lumen wall 2720, and the outer wall 2740 are all made ofthe same latex material and, therefore, together, form a very securelywater-tight connection. In an alternative exemplary embodiment, anadhesive can be used to bond the proximal end of the stretch-valve tube2820 to the inflation lumen wall 2720.

In such a configuration, therefore, any proximal movement of thecatheter 2700 at or proximal of the proximal port 2750 will also movethe stretch-valve tube 2820 proximally; in other words, the distal endof the stretch-valve tube 2820 can slide within the inflation lumen 2722in a proximal direction.

Reference is made to the flow chart of FIG. 41 to explain one exemplaryembodiment of a process for making a catheter according to theembodiment of FIGS. 37 and 38.

The catheter starts, in Step 4110 with a dual lumen extrusion of latex.This extrusion, therefore, defines the annular inner lumen wall 3710,3810 with the drainage lumen 3712, 3812 and, at one or morecircumferential longitudinal extents about the inner lumen wall 3710,3810, an inflation lumen wall 3720, 3820 with the inflation lumen 3722,3822. The dual lumen, therefore, already includes both the drainagelumen 2712, 2812 and the inflation lumen 2722, 2822. Both lumen 2712,2722, 2812, 2822, however, are extruded without obstruction and withoutradial ports. Therefore, in order to have the inflation port 3724, 3824,a radial hole needs to be created between the outside surface of theextrusion and the inflation lumen.

In Step 4112, the balloon inflation port 3724, 3824 is made tofluidically connect the environment of the extrusion to the inflationlumen 3722, 3822.

Different from the other exemplary embodiments described, with regard tothe embodiment of FIG. 37, the deflation port 3760 is created in Step4114 before, after, or at the same time as the balloon inflation port3724. The deflation port 3760 connects the interior of the balloon 3742to the interior of the drain lumen 3712. In an exemplary embodiment, thedeflation port 3760 is proximal of the balloon inflation port 3724 butcan be at or distal thereof.

Different from the other exemplary embodiments described, with regard tothe embodiment of FIG. 38, the drainage ports 3860 and 3862 are createdin Step 4114 before, after, or at the same time as the balloon inflationport 3824. The drainage port 3860 connects the interior of the balloon3842 to the interior of the drain lumen 2712 and the drainage port 3862connects the interior of the inflation lumen 3822 to the interior of thedrain lumen 2712. In an exemplary embodiment, the drainage ports 3860,3862 are aligned with the balloon inflation port 3824 but they can bedistal or proximal thereof. When aligned, a single through-hole can bemade through the entire catheter, penetrating both the inflation anddrainage channels 3712, 3722, 3812, 3822 and both walls 3710, 3720,3810, 3820 of the catheter. Alternatively, the drainage ports 3860, 3862can be spaced from one another with either one or neither aligned withthe inflation port 3824.

In Step 4116, a fixation through-hole 3732, 3832 is created through bothsides of the outer wall 3810 but not through the inflation lumen wall3720, 3820. This fixation through-hole 3732, 3832 will create themeasures for fixing the stretch-valve tube 3730, 3830 inside thedrainage lumen 3712, 3812. The fixation through-hole 3732, 3832 can beplaced anywhere proximal of the drainage ports 3760, 3860, 3862. Thefixation through-holes 3732, 3832 need not be aligned circumferentiallywith the inflation port 3724, 3824 if desired but the fixationthrough-holes 3732, 3832 are shown in FIGS. 37 and 38 as alignedtherewith. In the exemplary embodiment shown, the fixation through-hole3732, 3832 is still within the proximal end of the balloon 3842 but itcan equally be further proximal of the balloon 3842 to any length.

Sealing off of the distal end of the inflation lumen 3722, 3822 can beperformed in Step 4118 by inserting or creating a plug 3736, 3836therein or the sealing can occur before forming the fixation ports orjust before or simultaneously with the creation of the outer wall 3740,3840 below in Step 4124.

In Step 4120, the stretch-valve tube 3730, 3830 is inserted into thedrainage lumen 3712, 3812 and aligned so that the stretch-valve tube3730, 3830 covers all drainage ports 3760, 3860, 3862 and all of thefixation through-holes 3732, 3832. The distal end of the stretch-valvetube 3730, 3830 is positioned at the distal distance S desired foroperation of the stretch valve. For example, the distance can be up to 1mm, up to 2 mm, up to 3 mm and up to even 1 or 2 cm. The distance S canalso be dependent on the amount of stretch at the proximal end of thecatheter as the displacement of the stretch-valve tube is proportionalto the stretch of the catheter. For example, if the catheter is 500 mmlong and is pulled 20%, then it will be 600 mm long (a 100 mm stretch).A 10 mm or longer stretch-valve tube made from a stiff material, such asmetal (e.g., stainless steel, titanium, etc.) polycarbonate, polyimide,polyamide, polyurethane (Shore 55 D-75 D), and the like, located nearthe balloon of the catheter has its proximal end glued to the inside ofthe inflation or drainage lumen. When this catheter is stretched than20%, then the distal tip of a 10 mm stretch valve will move 2 mm in theproximal direction. Accordingly, if the drainage port(s) is placed 2 mmproximal to the distal end of the stretch-valve tube (here, S=2 mm), itwill remain sealed by the stretch-valve tube at a stretch of about 20%.But, when the catheter is pulled slightly more than 20% (or 2 mm), thedrainage port will unseal and the inflation fluid within the balloonwill discharge out the drainage port. As catheters vary amongmanufacturers, calibration of the percent stretch to the force requiredto stretch the catheter can be done for each different type of catheter.This force is defined in engineering terms as a modulus of the catheterand is a function of the modulus of the material and the effective wallthickness of the catheter. Low modulus materials and catheters willstretch more than high modulus materials and catheters when exposed tothe same force. Exemplary catheters are those made from latex rubber orsilicone rubber. Silicone rubber generally has a higher modulus thanlatex and, therefore, more force is required to stretch the cathetersufficiently to discharge the pressure within the balloon. Those ofskill in the art, therefore, will understand that different stretchvalves lengths can provided to dump the balloon pressure as a functionof a tug-force on the different catheters made from the differentmaterials and having different wall thicknesses. Accordingly, eventhough the stretch-valve tube distances are given, they are exemplaryand can change for different catheters having differentmaterials/thicknesses. As such, these exemplary distances for actuatingthe stretch-valve tube applies to all embodiments described herein butare not limited thereto.

If the fixation through-holes 3732, 3832 are within the inflationexpanse of the balloon sleeve (as shown), then an adhesive can be usedwithin the fixation through-holes 3732, 3832 to fix the proximal end ofthe stretch-valve tube 3730, 3830 thereat before attachment of theballoon sleeve. If the fixation through-holes 3732, 3832 are within theexpanse of the balloon sleeve but only overlap at the fixed proximal endof the balloon sleeve (not illustrated), then the same adhesive thatfixes the proximal end of the balloon sleeve can be used within thefixation through-holes 3732, 3832 to fix the proximal end of thestretch-valve tube 3730, 3830 thereat. Finally, if the fixationthrough-holes 3732, 3832 are outside the expanse of the balloon sleeveproximally, then an adhesive or the same material that creates the outerwall 3740, 3840 (see below) can be used within the fixationthrough-holes 3732, 3832 to fix the proximal end of the stretch-valvetube 3730, 3830.

In Step 4122, the balloon sleeve is placed about the inflation port3724, 3824 and the fixation through-holes 3732, 3832 (if the fixationthrough-holes 3732, 3832 are within the expanse of the balloon sleeve)and the balloon sleeve is fixed to the exterior of the inner andinflation lumen walls 3710, 3720, 3810, 3820 at both ends to define afluid-tight balloon interior therebetween. As such, inflation of theballoon 3742, 3842 can occur through the inflation lumen 3722, 3822. Forexample, the balloon sleeve making up the inner wall of the balloon3742, 3842 is slid over the distal end of the dual-lumen extrusion tocover at least the inflation port 3724, 3824 and is fluid-tightly sealedto the inner multi-lumen extrusion at both ends of the balloon sleevebut not in the intermediate portion. The balloon sleeve can be made oflatex as well and, therefore, can be secured to the latex multi-lumenextrusion in any known way to bond latex in a fluid-tight manner.

In Step 4124, the entire sub-assembly is covered with the outer wall3740, 3840. For example, the entire sub-assembly is dipped into latex inits liquid form to create the outer wall 3740, 3840. In the alternativeembodiment where a distal inflation lumen plug 3736, 3836 is not used,the latex can be allowed to enter at least a portion of the distal endof the inflation lumen 3722, 3822 but not so far as to block theinflation port 3724, 3824. When the latex cures, the balloon 3742, 3842is fluid tight and can only be fluidically connected to the environmentthrough the proximal-most opening of the inflation port, which isfluidically connected to the inflation lumen 3722, 3822. In thisprocess, the inner wall 3710, 3810, the inflation lumen wall 3720, 3820,the plug 3736, 3836, the balloon wall, and the outer wall 3740, 3840 areall made of the same latex material and, therefore, together, form avery securely water-tight balloon 3742, 3842.

In such a configuration, therefore, any proximal movement of thecatheter 3700, 3800 at or proximal of the proximal anchor 3732, 3832will also move the stretch-valve tube 3730, 3830 proximally; in otherwords, the distal end of the stretch-valve tube 3730, 3830 can slidewithin the inflation lumen 3722, 3822 in a proximal direction.

The steps outlined above in the exemplary embodiments need not be donein the order described or illustrated. Any of these steps can occur inany order to create the catheter according to the various exemplaryembodiments.

The catheters 200, 300, 1000, 1600, 2100, 2400, 2700, 3300, 3400, 3500,3600, 3700, 3800 according to the invention can be used in vascularapplications. It is known that every vessel has a tearing pressure.Balloons are used in coronary arteries, for example. If a coronaryartery balloon were to burst, there would be less damage if the burstwas controlled according to the invention. The same is true for a renalor iliac blood vessel. In such situations, the breakaway catheterimproves upon existing catheters by making them safer. From the urinarystandpoint, the breakaway balloon will not only prevent injury, but willalso be a signal to the technician that he/she needs to obtain theassistance of a physician or urologist with respect to inserting thecatheter.

We claim:
 1. A safety catheter, comprising: a flexible, multi-lumenshaft having an outer diameter, a distal tip, and a proximal catheterend with a drain end, the multi-lumen shaft defining: a drain lumenextending through the shaft and shaped to drain fluid adjacent thedistal tip therethrough and out the drain end; a distal hollow balloonportion defining a balloon interior and having at least one inflationport fluidically connected to the balloon interior, the balloon portioninflating outwardly to a diameter greater than the outer diameter of theshaft when inflated with inflation fluid; at least one inflation lumenparallel to the drain lumen and fluidically connected to the ballooninterior through the at least one inflation port, the at least oneinflation lumen shaped to inflate the balloon interior with theinflation fluid; and a drainage port fluidically connecting the ballooninterior to the drain lumen; and a hollow stretch valve: coaxiallydisposed in the drain lumen and shaped to permit fluid to passtherethrough; having a distal sliding portion slidably disposed withinthe drain lumen; positioned in the drain lumen such that: in a steadystate, the stretch valve prevents the inflation fluid from passingthrough the drainage port; and in a stretched state when the proximalcatheter end is stretched, the distal sliding portion slides within thedrain lumen to permit the inflation fluid to pass through the drainageport and into the drain lumen.